Stylets for use with apparatus for intravascular placement of a catheter

ABSTRACT

An integrated catheter placement system for accurately placing a catheter within a patient&#39;s vasculature is disclosed. In one embodiment, the integrated system comprises a system console, a tip location sensor for temporary placement on the patient&#39;s chest, and an ultrasound probe. The tip location sensor senses a magnetic field of a stylet disposed in a lumen of the catheter when the catheter is disposed in the vasculature. The ultrasound probe ultrasonically images a portion of the vasculature prior to introduction of the catheter. ECG signal-based catheter tip guidance is included in the integrated system to enable guidance of the catheter tip to a desired position with respect to a node of the patient&#39;s heart. Stylets and catheters including various multiple bipolar and monopolar electrode configurations are also disclosed.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims the benefit of U.S. Provisional Patent Application No. 61/246,957, filed Sep. 29, 2009, and entitled “Multi-Electrode ECG-Assisted System for Positioning a Catheter Within a Vasculature of a Patient.” This application is also a continuation-in-part of U.S. application Ser. No. 12/557,401, filed Sep. 10, 2009 now U.S. Pat. No. 8,849,382, and entitled “Apparatus and Display Methods Relating to Intravascular Placement of a Catheter,” which is a continuation-in-part of U.S. application Ser. No. 12/426,175, filed Apr. 17, 2009, and entitled “Systems and Methods for Breaching a Sterile Field for Intravascular Placement of a Catheter,” which is a continuation-in-part of U.S. application Ser. No. 12/323,273, filed Nov. 25, 2008, and entitled “Integrated System for Intravascular Placement of a Catheter,” now U.S. Pat. No. 8,388,541, which claims the benefit of the following U.S. Provisional Patent Applications: Application No. 60/990,242, filed Nov. 26, 2007, and entitled “Integrated Ultrasound and Tip Location System for Intravascular Placement of a Catheter;” Application No. 61/095,921, filed Sep. 10, 2008, and entitled “System and Method for Placing a Catheter Within a Vasculature of a Patient;” Application No. 61/091,233, filed Aug. 22, 2008, and entitled “Catheter Including Preloaded Steerable Stylet;” Application No. 61/095,451, filed Sep. 9, 2008, and entitled “Catheter Assembly Including ECG and Magnetic-Based Sensor Stylet;” and Application No. 61/045,944, filed Apr. 17, 2008, and entitled “Drape-Breaching Electrical Connector.” Each of the afore-referenced applications is incorporated herein by reference in its entirety.

BRIEF SUMMARY

Briefly summarized, embodiments of the present invention are directed to an integrated catheter placement system configured for accurately placing a catheter within the vasculature of a patient. The integrated system employs at least two modalities for improving catheter placement accuracy: 1) ultrasound-assisted guidance for introducing the catheter into the patient's vasculature; and 2) a tip location system (“TLS”), or magnetically-based (e.g., via permanent magnet(s) or electromagnet(s)) tracking of the catheter tip during its advancement through the vasculature to detect and facilitate correction of any tip malposition during such advancement.

In one embodiment, the integrated system comprises a system console including a control processor, a tip location sensor for temporary placement on a portion of a body of the patient, and an ultrasound probe. The tip location sensor senses a magnetic field of a stylet disposed in a lumen of the catheter when the catheter is disposed in the vasculature. The ultrasound probe ultrasonically images a portion of the vasculature prior to introduction of the catheter into the vasculature. In addition, the ultrasound probe includes user input controls for controlling use of the ultrasound probe in an ultrasound mode and use of the tip location sensor in a tip location mode.

In another embodiment, a third modality, i.e., ECG signal-based catheter tip guidance, is included in the system to enable guidance of the catheter tip to a desired position with respect to a node of the patient's heart from which the ECG signals originate. Various means for establishing a conductive pathway between a sterile field of the patient and a non-sterile field to enable passage of ECG signals from the catheter to the tip location sensor are also disclosed. Such means include, for example, connector schemes that establish the conductive pathway through a perforation defined in a sterile barrier, such as a surgical drape, wherein the perforation is isolated by the connector scheme so as to prevent contamination or compromise of the sterile field of the patient. In further embodiments, various aspects for visualizing and manipulating display of the ECG signal data acquired via the present catheter placement system are disclosed. These display aspects enable a clinician placing the catheter or other invasive medical device to ascertain information relating to the proximity of the device relative to the ECG signal-emitting node. In yet other embodiments, aspects of various ECG sensor configurations are also disclosed.

In further embodiments, stylets and catheters are disclosed that include various multi-electrode configurations. Including bipolar and monopolar electrodes, the stylets and catheters described in connection with certain embodiments enable an ECG wave filtering process to be followed, resulting in a relatively simple determination of catheter distal tip position within the vasculature.

These and other features of embodiments of the present invention will become more fully apparent from the following description and appended claims, or may be learned by the practice of embodiments of the invention as set forth hereinafter.

BRIEF DESCRIPTION OF THE DRAWINGS

A more particular description of the present disclosure will be rendered by reference to specific embodiments thereof that are illustrated in the appended drawings. It is appreciated that these drawings depict only typical embodiments of the invention and are therefore not to be considered limiting of its scope. Example embodiments of the invention will be described and explained with additional specificity and detail through the use of the accompanying drawings in which:

FIG. 1 is a block diagram depicting various elements of an integrated system for intravascular placement of a catheter, according to one example embodiment of the present invention;

FIG. 2 is a simplified view of a patient and a catheter being inserted therein with assistance of the integrated system of FIG. 1;

FIGS. 3A and 3B are views of a probe of the integrated system of FIG. 1;

FIG. 4 is a screenshot of an ultrasound image as depicted on a display of the integrated system of FIG. 1;

FIG. 5 is a perspective view of a stylet employed in connection with the system of FIG. 1 in placing a catheter within a patient vasculature;

FIG. 6 is an icon as depicted on a display of the integrated system of FIG. 1, indicating a position of a distal end of the stylet of FIG. 5 during catheter tip placement procedures;

FIGS. 7A-7E depict various example icons that can be depicted on the display of the integrated system of FIG. 1 during catheter tip placement procedures;

FIGS. 8A-8C are screenshots of images depicted on a display of the integrated system of FIG. 1 during catheter tip placement procedures;

FIG. 9 is a block diagram depicting various elements of an integrated system for intravascular placement of a catheter, according to another example embodiment of the present invention;

FIG. 10 is a simplified view of a patient and a catheter being inserted therein with assistance of the integrated system of FIG. 9;

FIG. 11 is a perspective view of a stylet employed in connection with the integrated system of FIG. 9 in placing a catheter within a patient vasculature;

FIGS. 12A-12E are various views of portions of the stylet of FIG. 11;

FIGS. 13A-13D are various views of a fin connector assembly for use with the integrated system of FIG. 9;

FIGS. 13E-13F are various views of a tether connector for use with the fin connector assembly shown in FIGS. 13A-13D;

FIGS. 14A-14C are views showing the connection of a stylet tether and fin connector to a sensor of the integrated system of FIG. 9;

FIG. 15 is a cross sectional view of the connection of the stylet tether, fin connector, and sensor shown in FIG. 14C;

FIG. 16 is simplified view of an ECG trace of a patient;

FIG. 17 is a screenshot of an image depicted on a display of the integrated system of FIG. 9 during catheter tip placement procedures;

FIG. 18 is a cross sectional view of a fin connector including electrical contacts configured in accordance with one embodiment;

FIGS. 19A and 19B are simplified views of an electrical contact retention system for engagement of a tether connector with a fin connector, in accordance with one embodiment;

FIGS. 20A-20C are various views of one embodiment of a fin connector and a tether connector for establishing a signal pathway through a sterile barrier in connection with use of the integrated system described herein;

FIGS. 21A and 21B are various views of a connector for electrically connecting ECG electrodes to a sensor of the integrated system, according to one embodiment;

FIGS. 22A-22C are various views of one embodiment of a fin connector and a tether connector for establishing a signal pathway through a sterile barrier;

FIGS. 23A and 23B are cross sectional views of a connector system for establishing a signal pathway through a sterile barrier, according to one embodiment;

FIG. 24 is a simplified side view of a connector system for establishing a signal pathway through a sterile barrier, according to one embodiment;

FIGS. 25A and 25B are simplified side views of a connector system for establishing a signal pathway through a sterile barrier, according to one embodiment;

FIGS. 26A and 26B are cross sectional views of a connector system for establishing a signal pathway through a sterile barrier, according to one embodiment;

FIG. 27 is a simplified view of a connector system for establishing a signal pathway through a sterile barrier, according to one embodiment;

FIG. 28 is a perspective view of stylet including a sterile shield for use with the connector system shown in FIG. 28, according to one embodiment;

FIGS. 29A and 29B are simplified views of the ECG module of FIG. 27, including a connector system for establishing a signal pathway through a sterile barrier, according to one embodiment;

FIG. 30 is a simplified view of a connector system for establishing a signal pathway through a sterile barrier, according to one embodiment;

FIG. 31 is a simplified view of a connector system for establishing a signal pathway through a sterile barrier, according to one embodiment;

FIG. 32 is a simplified view of elements of a connector system for establishing a signal pathway through a sterile barrier, according to one embodiment;

FIG. 33 is a view of a means for establishing a conductive pathway between sterile and non-sterile fields, according to one embodiment;

FIG. 34 is a view of another means for establishing a conductive pathway between sterile and non-sterile fields, according to one embodiment;

FIGS. 35A-C depict exemplary P-wave waveforms;

FIG. 36 is a view of a sensor retro-fitted with a wireless module, according to one embodiment;

FIG. 37 is a view of a retention feature for a connector, according to one embodiment;

FIG. 38 is a perspective view of a catheter including an ECG sensor according to one embodiment;

FIG. 39 is a perspective view of a sensor assembly including multiple electrodes disposed on a catheter;

FIGS. 40A-40C depict operation of the catheter of FIG. 39;

FIGS. 41A-41D are various views of an electrode connection integrity indicator and system in accordance with one embodiment;

FIG. 42 is a perspective view of an electrode connection integrity system according to one embodiment;

FIGS. 43A and 43B are cross sectional views of a stylet including a conductive wire loop for detecting severing of the stylet according to one embodiment;

FIG. 44 is a partial cross sectional view the stylet of FIG. 43A, including a conductive wire loop with a planar wire in accordance with one embodiment;

FIG. 45 is a cross sectional view of a catheter including a stylet with a distal interference feature according to one embodiment;

FIG. 46 is a cross sectional view of a catheter including a stylet with a distal interference feature according to another embodiment;

FIGS. 47A and 47B are cross sectional views of distal portions of a catheter and stylet configured to maintain alignment of the distal ends of the catheter and stylet according to one embodiment.

FIG. 48 is a perspective view of an external dual-ECG electrode assembly in accordance with one embodiment;

FIG. 49 is a perspective view of an external ECG electrode assembly including graphics in accordance with one embodiment;

FIG. 50 is an ECG trace showing P-wave characteristics according to one embodiment;

FIG. 51 is a flow chart describing one method according to one embodiment;

FIGS. 52-55 are ECG traces showing additional P-wave characteristics according to embodiments of the present disclosure;

FIGS. 56A-57B are ECG traces showing details regarding ECG waveform scaling according to one embodiment;

FIG. 58 is a flow chart describing one method according to one embodiment;

FIG. 59 is a display window including aspects of a single ECG waveform according to one embodiment;

FIG. 60 is a flow chart describing one method according to one embodiment;

FIG. 61 is a catheter placement record configured according to one embodiment;

FIG. 62 is another catheter placement record configured according to one embodiment;

FIG. 63 is a simplified view of a patient and a catheter being inserted therein with assistance of the integrated system of FIG. 1;

FIGS. 64A and 64B show various views of a multi-electrode stylet in accordance with one embodiment;

FIGS. 65A-65C show various details regarding filtering of ECG waveforms in accordance with one embodiment;

FIG. 66 shows a possible peak plot that depicts positions of portions of the multi-electrode stylet of FIGS. 64A and 64B with respect to a signal producing node of a patient's heart;

FIG. 67 is a view of a catheter and stylet disposed proximate a patient's heart according to one embodiment;

FIGS. 68A-68D show other possible peak plots according to another embodiment;

FIGS. 69A-69C show further details regarding filtered ECG waveforms according to one embodiment;

FIG. 69D shows various stages of a method for positioning a catheter within a vasculature according to one embodiment;

FIGS. 70A-70D show various possible screenshots for depicting proximity of a multi-electrode stylet with respect to a patient's heart in accordance with one embodiment;

FIG. 71 shows another possible screenshot for depicting proximity of a multi-electrode stylet with respect to a patient's heart in accordance with one embodiment;

FIG. 72 shows various possible multi-electrode configurations for a stylet according to one embodiment;

FIG. 73 shows a relationship between stylet electrode position and QRS wave complex morphology;

FIGS. 74 and 74B show details of an atraumatic tip for a multi-electrode stylet according to one embodiment;

FIGS. 75A-75F show use of the stylet with atraumatic tip of FIGS. 74A and 74B according to one embodiment;

FIGS. 76A and 76B show details of a multi-electrode stylet including an atraumatic tip according to one embodiment;

FIGS. 77A and 77B show details of a multi-electrode stylet including an atraumatic tip according to one embodiment;

FIGS. 78A and 78B show details of a multi-electrode stylet including an atraumatic tip according to one embodiment;

FIGS. 79A and 79B show details of a multi-electrode stylet including an atraumatic tip according to one embodiment;

FIGS. 80A and 80B show details of a multi-electrode stylet including an atraumatic tip according to one embodiment;

FIGS. 81-83 are various views of an electrode for use with a catheter, according to one embodiment;

FIG. 84 is a perspective view of a catheter including a conductive element according to one embodiment;

FIG. 85 is a partial cutaway view of the catheter of FIG. 84 with a multi-electrode stylet disposed in a lumen thereof;

FIG. 86 is a partial cutaway view of a catheter including conductive elements with a multi-electrode stylet disposed in a lumen thereof;

FIGS. 87A-87D are various views of a trimmable catheter including annular conductive elements with a multi-electrode stylet for disposal within a lumen thereof;

FIGS. 88A and 88B show examples of a catheter including an internal stylet lumen, according to one embodiment;

FIGS. 89A and 89B show various views of a catheter including an internal stylet lumen and insulated stylet according to one embodiment;

FIGS. 90A and 90B show various views of a catheter including a valved, internal stylet lumen according to one embodiment;

FIGS. 91A and 91B show various views of an optical fiber-based stylet according to one embodiment;

FIGS. 92A and 92B show various views of a connector for use with the stylet of FIGS. 91A and 91B, according to one embodiment;

FIG. 93 is a partial cutaway view of an optical fiber-based stylet according to one embodiment;

FIG. 94 shows an assembly for performing laser speckle imaging using an optical fiber-based stylet, according to one embodiment;

FIGS. 95A and 95B show a distal end of an optical fiber-based stylet configured to enable optical pressure sensing, according to one embodiment;

FIG. 96 shows a distal portion of a stylet including an AC resonance coil, according to one embodiment;

FIG. 97 shows a distal portion of a stylet partially disposed in a catheter, including various sensing components, according to one embodiment;

FIG. 98 is a simplified view of catheter including the stylet shown in FIG. 97;

FIGS. 99A and 99B show various views of catheter and a wireless monitoring dongle in accordance with one embodiment;

FIGS. 100A-100C are various views of magnetic leaf valves configured in accordance with one embodiment;

FIG. 101 shows a light source/sensor assembly for use with a catheter in accordance with one embodiment;

FIGS. 102A-102C show various details of a wireless dongle for use with a catheter placement system according to one embodiment;

FIGS. 103A-E show various steps for placing the wireless dongle of FIGS. 102A-102C in a sterile bag, according to one embodiment; and

FIG. 104 shows the wireless dongle of FIGS. 102A-102C in use for measuring a catheter length prior to insertion into the patient, according to one embodiment.

DETAILED DESCRIPTION OF SELECTED EMBODIMENTS

Reference will now be made to figures wherein like structures will be provided with like reference designations. It is understood that the drawings are diagrammatic and schematic representations of exemplary embodiments of the present invention, and are neither limiting nor necessarily drawn to scale.

FIGS. 1-104 depict various features of embodiments of the present invention, which is generally directed to a catheter placement system configured for accurately placing a catheter within the vasculature of a patient. In one embodiment, the catheter placement system employs at least two modalities for improving catheter placement accuracy: 1) ultrasound-assisted guidance for introducing the catheter into the patient's vasculature; and 2) a tip location/navigation system (“TLS”), or magnetically-based tracking of the catheter tip during its advancement through the tortuous vasculature path to detect and facilitate correction of any tip malposition during such advancement. The ultrasound guidance and tip location features of the present system according to one embodiment are integrated into a single device for use by a clinician placing the catheter. Integration of these two modalities into a single device simplifies the catheter placement process and results in relatively faster catheter placements. For instance, the integrated catheter placement system enables ultrasound and TLS activities to be viewed from a single display of the integrated system. Also, controls located on an ultrasound probe of the integrated device, which probe is maintained within the sterile field of the patient during catheter placement, can be used to control functionality of the system, thus precluding the need for a clinician to reach out of the sterile field in order to control the system.

In another embodiment, a third modality, i.e., ECG signal-based catheter tip guidance, is included in the integrated system to enable guidance of the catheter tip to a desired position with respect to a node of the patient's heart from which the ECG signals originate. Such ECG-based positional assistance is also referred to herein as “tip confirmation.”

Combination of the three modalities above according to one embodiment enables the catheter placement system to facilitate catheter placement within the patient's vasculature with a relatively high level of accuracy, i.e., placement of the distal tip of the catheter in a predetermined and desired position. Moreover, because of the ECG-based guidance of the catheter tip, correct tip placement may be confirmed without the need for a confirmatory X-ray. This, in turn, reduces the patient's exposure to potentially harmful x-rays, the cost and time involved in transporting the patient to and from the x-ray department, costly and inconvenient catheter repositioning procedures, etc.

As the ECG signal-based modality includes a need for passing ECG signals from a catheter assembly disposed in a sterile field of a patient to a data-receiving component of the system disposed in a non-sterile field, embodiments of the present invention are further concerned with various connector systems for establishing a conductive pathway through a sterile barrier separating the sterile and non-sterile fields. Various aspects for visualizing and manipulating display of the ECG signal data acquired via the present system, together with aspects of various ECG sensor configurations, are also disclosed.

For clarity it is to be understood that the word “proximal” as used herein refers to a direction relatively closer to a clinician, while the word “distal” refers to a direction relatively further from the clinician. For example, the end of a catheter placed within the body of a patient is considered a distal end of the catheter, while the catheter end remaining outside the body is a proximal end of the catheter. Also, the words “including,” “has,” and “having,” as used herein, including the claims, shall have the same meaning as the word “comprising.”

Reference is first made to FIGS. 1 and 2 which depict various components of a catheter placement system (“system”), generally designated at 10, configured in accordance with one example embodiment of the present invention. As shown, the system 10 generally includes a console 20, display 30, probe 40, and sensor 50, each of which is described in further detail below.

FIG. 2 shows the general relation of these components to a patient 70 during a procedure to place a catheter 72 into the patient vasculature through a skin insertion site 73. FIG. 2 shows that the catheter 72 generally includes a proximal portion 74 that remains exterior to the patient and a distal portion 76 that resides within the patient vasculature after placement is complete. The system 10 is employed to ultimately position a distal tip 76A of the catheter 72 in a desired position within the patient vasculature. In one embodiment, the desired position for the catheter distal tip 76A is proximate the patient's heart, such as in the lower one-third (⅓^(rd)) portion of the Superior Vena Cava (“SVC”). Of course, the system 10 can be employed to place the catheter distal tip in other locations. The catheter proximal portion 74 further includes a hub 74A that provides fluid communication between the one or more lumens of the catheter 72 and one or more extension legs 74B extending proximally from the hub.

An example implementation of the console 20 is shown in FIG. 8C, though it is appreciated that the console can take one of a variety of forms. A processor 22, including non-volatile memory such as EEPROM for instance, is included in the console 20 for controlling system function during operation of the system 10, thus acting as a control processor. A digital controller/analog interface 24 is also included with the console 20 and is in communication with both the processor 22 and other system components to govern interfacing between the probe 40, sensor 50, and other system components.

The system 10 further includes ports 52 for connection with the sensor 50 and optional components 54 including a printer, storage media, keyboard, etc. The ports in one embodiment are USB ports, though other port types or a combination of port types can be used for this and the other interfaces connections described herein. A power connection 56 is included with the console 20 to enable operable connection to an external power supply 58. An internal battery 60 can also be employed, either with or exclusive of an external power supply. Power management circuitry 59 is included with the digital controller/analog interface 24 of the console to regulate power use and distribution.

The display 30 in the present embodiment is integrated into the console 20 and is used to display information to the clinician during the catheter placement procedure. In another embodiment, the display may be separate from the console. As will be seen, the content depicted by the display 30 changes according to which mode the catheter placement system is in: US, TLS, or in other embodiments, ECG tip confirmation. In one embodiment, a console button interface 32 (see FIGS. 1, 8C) and buttons included on the probe 40 can be used to immediately call up a desired mode to the display 30 by the clinician to assist in the placement procedure. In one embodiment, information from multiple modes, such as TLS and ECG, may be displayed simultaneously, such as in FIG. 17. Thus, the single display 30 of the system console 20 can be employed for ultrasound guidance in accessing a patient's vasculature, TLS guidance during catheter advancement through the vasculature, and (as in later embodiments) ECG-based confirmation of catheter distal tip placement with respect to a node of the patient's heart. In one embodiment, the display 30 is an LCD device.

FIGS. 3A and 3B depict features of the probe 40 according to one embodiment. The probe 40 is employed in connection with the first modality mentioned above, i.e., ultrasound (“US”)-based visualization of a vessel, such as a vein, in preparation for insertion of the catheter 72 into the vasculature. Such visualization gives real time ultrasound guidance for introducing the catheter into the vasculature of the patient and assists in reducing complications typically associated with such introduction, including inadvertent arterial puncture, hematoma, pneumothorax, etc.

The handheld probe 40 includes a head 80 that houses a piezoelectric array for producing ultrasonic pulses and for receiving echoes thereof after reflection by the patient's body when the head is placed against the patient's skin proximate the prospective insertion site 73 (FIG. 2). The probe 40 further includes a plurality of control buttons 84, which can be included on a button pad 82. In the present embodiment, the modality of the system 10 can be controlled by the control buttons 84, thus eliminating the need for the clinician to reach out of the sterile field, which is established about the patient insertion site prior to catheter placement, to change modes via use of the console button interface 32.

As such, in one embodiment a clinician employs the first (US) modality to determine a suitable insertion site and establish vascular access, such as with a needle or introducer, then with the catheter. The clinician can then seamlessly switch, via button pushes on the probe button pad 82, to the second (TLS) modality without having to reach out of the sterile field. The TLS mode can then be used to assist in advancement of the catheter 72 through the vasculature toward an intended destination.

FIG. 1 shows that the probe 40 further includes button and memory controller 42 for governing button and probe operation. The button and memory controller 42 can include non-volatile memory, such as EEPROM, in one embodiment. The button and memory controller 42 is in operable communication with a probe interface 44 of the console 20, which includes a piezo input/output component 44A for interfacing with the probe piezoelectric array and a button and memory input/output component 44B for interfacing with the button and memory controller 42.

FIG. 4 shows an example screenshot 88 as depicted on the display 30 while the system 10 is in its first ultrasound modality. An image 90 of a subcutaneous region of the patient 70 is shown, depicting a cross section of a vein 92. The image 90 is produced by operation of the piezoelectric array of the probe 40. also included on the display screenshot 88 is a depth scale indicator 94, providing information regarding the depth of the image 90 below the patient's skin, a lumen size scale 96 that provides information as to the size of the vein 92 relative to standard catheter lumen sizes, and other indicia 98 that provide information regarding status of the system 10 or possible actions to be taken, e.g., freeze frame, image templates, data save, image print, power status, image brightness, etc.

Note that while a vein is depicted in the image 90, other body lumens or portions can be imaged in other embodiments. Note that the US mode shown in FIG. 4 can be simultaneously depicted on the display 30 with other modes, such as the TLS mode, if desired. In addition to the visual display 30, aural information, such as beeps, tones, etc., can also be employed by the system 10 to assist the clinician during catheter placement. Moreover, the buttons included on the probe 40 and the console button interface 32 can be configured in a variety of ways, including the use of user input controls in addition to buttons, such as slide switches, toggle switches, electronic or touch-sensitive pads, etc. Additionally, both US and TLS activities can occur simultaneously or exclusively during use of the system 10.

As just described, the handheld ultrasound probe 40 is employed as part of the integrated catheter placement system 10 to enable US visualization of the peripheral vasculature of a patient in preparation for transcutaneous introduction of the catheter. In the present example embodiment, however, the probe is also employed to control functionality of the TLS portion, or second modality, of the system 10 when navigating the catheter toward its desired destination within the vasculature as described below. Again, as the probe 40 is used within the sterile field of the patient, this feature enables TLS functionality to be controlled entirely from within the sterile field. Thus the probe 40 is a dual-purpose device, enabling convenient control of both US and TLS functionality of the system 10 from the sterile field. In one embodiment, the probe can also be employed to control some or all ECG-related functionality, or third modality, of the catheter placement system 10, as described further below.

The catheter placement system 10 further includes the second modality mentioned above, i.e., the magnetically-based catheter TLS, or tip location system. The TLS enables the clinician to quickly locate and confirm the position and/or orientation of the catheter 72, such as a peripherally-inserted central catheter (“PICC”), central venous catheter (“CVC”), or other suitable catheter, during initial placement into and advancement through the vasculature of the patient 70. Specifically, the TLS modality detects a magnetic field generated by a magnetic element-equipped tip location stylet, which is pre-loaded in one embodiment into a longitudinally defined lumen of the catheter 72, thus enabling the clinician to ascertain the general location and orientation of the catheter tip within the patient body. In one embodiment, the magnetic assembly can be tracked using the teachings of one or more of the following U.S. Pat. Nos. 5,775,322; 5,879,297; 6,129,668; 6,216,028; and 6,263,230. The contents of the afore-mentioned U.S. patents are incorporated herein by reference in their entireties. The TLS also displays the direction in which the catheter tip is pointing, thus further assisting accurate catheter placement. The TLS further assists the clinician in determining when a malposition of the catheter tip has occurred, such as in the case where the tip has deviated from a desired venous path into another vein.

As mentioned, the TLS utilizes a stylet to enable the distal end of the catheter 72 to be tracked during its advancement through the vasculature. FIG. 5 gives an example of such a stylet 100, which includes a proximal end 100A and a distal end 100B. A handle 102 is included at the stylet proximal end 100A, with a core wire 104 extending distally therefrom. A magnetic assembly is disposed distally of the core wire 104. The magnetic assembly includes one or more magnetic elements 106 disposed adjacent one another proximate the stylet distal end 100B and encapsulated by tubing 108. In the present embodiment, a plurality of magnetic elements 106 is included, each element including a solid, cylindrically shaped ferromagnetic stacked end-to-end with the other magnetic elements. An adhesive tip 110 can fill the distal tip of the tubing 108, distally to the magnetic elements 106.

Note that in other embodiments, the magnetic elements may vary from the design in not only shape, but also composition, number, size, magnetic type, and position in the stylet distal segment. For example, in one embodiment, the plurality of ferromagnetic magnetic elements is replaced with an electromagnetic assembly, such as an electromagnetic coil, which produces a magnetic field for detection by the sensor. Another example of an assembly usable here can be found in U.S. Pat. No. 5,099,845 entitled “Medical Instrument Location Means,” which is incorporated herein by reference in its entirety. Yet other examples of stylets including magnetic elements that can be employed with the TLS modality can be found in U.S. Pat. No. 8,784,336, entitled “Stylet Apparatuses and Methods of Manufacture,” which is incorporated herein by reference in its entirety. These and other variations are therefore contemplated by embodiments of the present invention. It should appreciated herein that “stylet” as used herein can include any one of a variety of devices configured for removable placement within a lumen of the catheter to assist in placing a distal end of the catheter in a desired location within the patient's vasculature.

FIG. 2 shows disposal of the stylet 100 substantially within a lumen in the catheter 72 such that the proximal portion thereof extends proximally from the catheter lumen, through the hub 74A and out through a selected one of the extension legs 74B. So disposed within a lumen of the catheter, the distal end 100B of the stylet 100 is substantially co-terminal with the distal catheter end 76A such that detection by the TLS of the stylet distal end correspondingly indicates the location of the catheter distal end.

The TLS sensor 50 is employed by the system 10 during TLS operation to detect a magnetic field produced by the magnetic elements 106 of the stylet 100. As seen in FIG. 2, the TLS sensor 50 is placed on the chest of the patient during catheter insertion. The TLS sensor 50 is placed on the chest of the patient in a predetermined location, such as through the use of external body landmarks, to enable the magnetic field of the stylet magnetic elements 106, disposed in the catheter 72 as described above, to be detected during catheter transit through the patient vasculature. Again, as the magnetic elements 106 of the stylet magnetic assembly are co-terminal with the distal end 76A of the catheter 72 (FIG. 2), detection by the TLS sensor 50 of the magnetic field of the magnetic elements provides information to the clinician as to the position and orientation of the catheter distal end during its transit.

In greater detail, the TLS sensor 50 is operably connected to the console 20 of the system 10 via one or more of the ports 52, as shown in FIG. 1. Note that other connection schemes between the TLS sensor and the system console can also be used without limitation. As just described, the magnetic elements 106 are employed in the stylet 100 to enable the position of the catheter distal end 76A (FIG. 2) to be observable relative to the TLS sensor 50 placed on the patient's chest. Detection by the TLS sensor 50 of the stylet magnetic elements 106 is graphically displayed on the display 30 of the console 20 during TLS mode. In this way, a clinician placing the catheter is able to generally determine the location of the catheter distal end 76A within the patient vasculature relative o the TLS sensor 50 and detect when catheter malposition, such as advancement of the catheter along an undesired vein, is occurring.

FIGS. 6 and 7A-7E show examples of icons that can be used by the console display 30 to depict detection of the stylet magnetic elements 106 by the TLS sensor 50. In particular, FIG. 6 shows an icon 114 that depicts the distal portion of the stylet 100, including the magnetic elements 106 as detected by the TLS sensor 50 when the magnetic elements are positioned under the TLS sensor. As the stylet distal end 100B is substantially co-terminal with the distal end 76A of the catheter 72, the icon indicates the position and orientation of the catheter distal end. FIGS. 7A-7E show various icons that can be depicted on the on the console display 30 when the magnetic elements 106 of the stylet 100 are not positioned directly under a portion of the TLS sensor 50, but are nonetheless detected nearby. The icons can include half-icons 114A and quarter-icons 114B that are displayed according to the position of the stylet magnetic assembly, i.e., the magnetic elements 106 in the present embodiment, relative to the TLS sensor 50.

FIGS. 8A-8C depict screenshots taken from the display 30 of the system 10 while in TLS mode, showing how the magnetic assembly of the stylet 100 is depicted. The screenshot 118 of FIG. 8A shows a representative image 120 of the TLS sensor 50. Other information is provided on the display screenshot 118, including a depth scale indicator 124, status/action indicia 126, and icons 128 corresponding to the button interface 32 included on the console 20 (FIG. 8C). Though the icons 128 in the present embodiment are simply indicators to guide the user in identifying the purpose of the corresponding buttons of the button interface 32, in another embodiment the display can be made touch-sensitive so that the icons themselves can function as button interfaces and can change according to the mode the system is in.

During initial stages of catheter advancement through the patient's vasculature after insertion therein, the distal end 76A of the catheter 72, having the stylet distal end 100B substantially co-terminal therewith, is relatively distant from the TLS sensor 50. As such, the display screenshot will indicate “no signal,” indicating that the magnetic field from the stylet magnetic assembly has not been detected. In FIG. 8B, the magnetic assembly proximate the stylet distal end 100B has advanced sufficiently close to the TLS sensor 50 to be detected thereby, though it is not yet under the sensor. This is indicated by the half-icon 114A shown to the left of the sensor image 120, representing the stylet magnetic assembly being positioned to the right of the TLS sensor 50 from the perspective of the patient.

In FIG. 8C, the magnetic assembly proximate the stylet distal end 100B has advanced under the TLS sensor 50 such that its position and orientation relative thereto is detected by the TLS sensor. This is indicated by the icon 114 on the sensor image 120. Note that the button icons 128 provide indications of the actions that can be performed by pressing the corresponding buttons of the console button interface 32. As such, the button icons 128 can change according to which modality the system 10 is in, thus providing flexibility of use for the button interface 32. Note further that, as the button pad 82 of the probe 40 (FIG. 3A, 3B) includes buttons 84 that mimic several of the buttons of the button interface 32, the button icons 128 on the display 30 provide a guide to the clinician for controlling the system 10 with the probe buttons 84 while remaining in the sterile field. For instance, if the clinician has need to leave TLS mode and return to US (ultrasound) mode, the appropriate control button 84 on the probe button pad 82 can be depressed, and the US mode can be immediately called up, with the display 30 refreshing to accommodate the visual information needed for US functionality, such as that shown in FIG. 4. This is accomplished without a need for the clinician to reach out of the sterile field.

Reference is now made to FIGS. 9 and 10 in describing the integrated catheter placement system 10 according to another example embodiment. As before, the integrated system 10 includes the console 20, display 30, probe 40 for US functionality, and the TLS sensor 50 for tip location functionality as described above. Note that the system 10 depicted in FIGS. 9 and 10 is similar in many respects to the system shown in FIGS. 1 and 2. As such, only selected differences will be discussed below. The system 10 of FIGS. 9 and 10 includes additional functionality wherein determination of the proximity of the catheter distal tip 76A relative to a sino-atrial (“SA”) or other electrical impulse-emitting node of the heart of the patient 70 can be determined, thus providing enhanced ability to accurately place the catheter distal tip in a desired location proximate the node. Also referred to herein as “ECG” or “ECG-based tip confirmation,” this third modality of the system 10 enables detection of ECG signals from the SA node in order to place the catheter distal tip in a desired location within the patient vasculature. Note that the US, TLS, and ECG modalities are seamlessly combined in the present system 10, but can be employed in concert or individually to assist in catheter placement. In one embodiment, it is understood that the ECG modality as described herein can be included in a stand-alone system without the inclusion of the US and TLS modalities. Thus, the environments in which the embodiments herein are described are understood as merely example environments and are not considered limiting of the present disclosure.

FIGS. 9 and 10 show the addition to the system 10 of a stylet 130 configured in accordance with the present embodiment. As an overview, the catheter stylet 130 is removably predisposed within the lumen of the catheter 72 being inserted into the patient 70 via the insertion site 73. The stylet 130, in addition to including a magnetic assembly for the magnetically-based TLS modality, includes a sensing component, i.e., an ECG sensor assembly, proximate its distal end and including a portion that is co-terminal with the distal end of the catheter tip for sensing ECG signals produced by the SA node. In contrast to the previous embodiment, the stylet 130 includes a tether 134 extending from its proximal end that operably connects to the TLS sensor 50. As will be described in further detail, the stylet tether 134 permits ECG signals detected by the ECG sensor assembly included on a distal portion of the stylet 130 to be conveyed to the TLS sensor 50 during confirmation of the catheter tip location as part of the ECG signal-based tip confirmation modality. Reference and ground ECG lead/electrode pairs 158 attach to the body of the body of the patient 70 and are operably attached to the TLS sensor 50 to enable the system to filter out high level electrical activity unrelated to the electrical activity of the SA node of the heart, thus enabling the ECG-based tip confirmation functionality. Together with the reference and ground signals received from the ECG lead/electrode pairs 158 placed on the patient's skin, the ECG signals sensed by the stylet ECG sensor assembly are received by the TLS sensor 50 positioned on the patient's chest (FIG. 10) or other designated component of the system 10. The TLS sensor 50 and/or console processor 22 can process the ECG signal data to produce an electrocardiogram waveform on the display 30, as will be described. In the case where the TLS sensor 50 processes the ECG signal data, a processor is included therein to perform the intended functionality. If the console 20 processes the ECG signal data, the processor 22, controller 24, or other processor can be utilized in the console to process the data.

Thus, as it is advanced through the patient vasculature, the catheter 72 equipped with the stylet 130 as described above can advance under the TLS sensor 50, which is positioned on the chest of the patient as shown in FIG. 10. This enables the TLS sensor 50 to detect the position of the magnetic assembly of the stylet 130, which is substantially co-terminal with the distal tip 76A of the catheter as located within the patient's vasculature. The detection by the TLS sensor 50 of the stylet magnetic assembly is depicted on the display 30 during ECG mode. The display 30 further depicts during ECG mode an ECG electrocardiogram waveform produced as a result of patient heart's electrical activity as detected by the ECG sensor assembly of the stylet 130. In greater detail, the ECG electrical activity of the SA node, including the P-wave of the waveform, is detected by the ECG sensor assembly of the stylet (described below) and forwarded to the TLS sensor 50 and console 20. The ECG electrical activity is then processed for depiction on the display 30. A clinician placing the catheter can then observe the ECG data to determine optimum placement of the distal tip 76A of the catheter 72, such as proximate the SA node in one embodiment. In one embodiment, the console 20 includes the electronic components, such as the processor 22 (FIG. 9), necessary to receive and process the signals detected by the stylet ECG sensor assembly. In another embodiment, the TLS sensor 50 can include the necessary electronic components processing the ECG signals.

As already discussed, the display 30 is used to display information to the clinician during the catheter placement procedure. The content of the display 30 changes according to which mode the catheter placement system is in: US, TLS, or ECG. Any of the three modes can be immediately called up to the display 30 by the clinician, and in some cases information from multiple modes, such as TLS and ECG, may be displayed simultaneously. In one embodiment, as before, the mode the system is in may be controlled by the control buttons 84 included on the handheld probe 40, thus eliminating the need for the clinician to reach out of the sterile field (such as touching the button interface 32 of the console 20) to change modes. Thus, in the present embodiment the probe 40 is employed to also control some or all ECG-related functionality of the system 10. Note that the button interface 32 or other input configurations can also be used to control system functionality. Also, in addition to the visual display 30, aural information, such as beeps, tones, etc., can also be employed by the system to assist the clinician during catheter placement.

Reference is now made to FIGS. 11-12E in describing various details of one embodiment of the stylet 130 that is removably loaded into the catheter 72 and employed during insertion to position the distal tip 76A of the catheter in a desired location within the patient vasculature. As shown, the stylet 130 as removed from the catheter defines a proximal end 130A and a distal end 130B. A connector 132 is included at the proximal stylet end 130A, and a tether 134 extends distally from the connector and attaches to a handle 136. A core wire 138 extends distally from the handle 136. The stylet 130 is pre-loaded within a lumen of the catheter 72 in one embodiment such that the distal end 130B is substantially flush, or co-terminal, with the catheter opening at the distal end 76A thereof (FIG. 10), and such that a proximal portion of the core wire 138, the handle 136, and the tether 134 extend proximally from a selected one of the extension tubes 74B. Note that, though described herein as a stylet, in other embodiments a guidewire or other catheter guiding apparatus could include the principles of the embodiment described herein.

The core wire 138 defines an elongate shape and is composed of a suitable stylet material including stainless steel or a memory material such as, in one embodiment, a nickel and titanium-containing alloy commonly known by the acronym “nitinol.” Though not shown here, manufacture of the core wire 138 from nitinol in one embodiment enables the portion of the core wire corresponding to a distal segment of the stylet to have a pre-shaped bent configuration so as to urge the distal portion of the catheter 72 into a similar bent configuration. In other embodiments, the core wire includes no pre-shaping. Further, the nitinol construction lends torqueability to the core wire 138 to enable a distal segment of the stylet 130 to be manipulated while disposed within the lumen of the catheter 72, which in turn enables the distal portion of the catheter to be navigated through the vasculature during catheter insertion.

The handle 136 is provided to enable insertion/removal of the stylet from the catheter 72. In embodiments where the stylet core wire 138 is torqueable, the handle 136 further enables the core wire to be rotated within the lumen of the catheter 72, to assist in navigating the catheter distal portion through the vasculature of the patient 70.

The handle 136 attaches to a distal end of the tether 134. In the present embodiment, the tether 134 is a flexible, shielded cable housing one or more conductive wires electrically connected both to the core wire 138, which acts as the ECG sensor assembly referred to above, and the tether connector 132. As such, the tether 134 provides a conductive pathway from the distal portion of the core wire 138 through to the tether connector 132 at proximal end 130A of the stylet 130. As will be explained, the tether connector 132 is configured for operable connection to the TLS sensor 50 on the patient's chest for assisting in navigation of the catheter distal tip 76A to a desired location within the patient vasculature.

As seen in FIGS. 12B-12D, a distal portion of the core wire 138 is gradually tapered, or reduced in diameter, distally from a junction point 142. A sleeve 140 is slid over the reduced-diameter core wire portion. Though of relatively greater diameter here, the sleeve in another embodiment can be sized to substantially match the diameter of the proximal portion of the stylet core wire. The stylet 130 further includes a magnetic assembly disposed proximate the distal end 130B thereof for use during TLS mode. The magnetic assembly in the illustrated embodiment includes a plurality of magnetic elements 144 interposed between an outer surface of the reduced-diameter core wire 138 and an inner surface of the sleeve 140 proximate the stylet distal end 130B. In the present embodiment, the magnetic elements 144 include 20 ferromagnetic magnets of a solid cylindrical shape stacked end-to-end in a manner similar to the stylet 100 of FIG. 2. In other embodiments, however, the magnetic element(s) may vary from this design in not only shape, but also composition, number, size, magnetic type, and position in the stylet. For example, in one embodiment the plurality of magnets of the magnetic assembly is replaced with an electromagnetic coil that produces a magnetic field for detection by the TLS sensor. These and other variations are therefore contemplated by embodiments of the present invention.

The magnetic elements 144 are employed in the stylet 130 distal portion to enable the position of the stylet distal end 130B to be observable relative to the TLS sensor 50 placed on the patient's chest. As has been mentioned, the TLS sensor 50 is configured to detect the magnetic field of the magnetic elements 144 as the stylet advances with the catheter 72 through the patient vasculature. In this way, a clinician placing the catheter 72 is able to generally determine the location of the catheter distal end 76A within the patient vasculature and detect when catheter malposition is occurring, such as advancement of the catheter along an undesired vein, for instance.

The stylet 130 further includes the afore-mentioned ECG sensor assembly, according to one embodiment. The ECG sensor assembly enables the stylet 130, disposed in a lumen of the catheter 72 during insertion, to be employed in detecting an intra-atrial ECG signal produced by an SA or other node of the patient's heart, thereby allowing for navigation of the distal tip 76A of the catheter 72 to a predetermined location within the vasculature proximate the patient's heart. Thus, the ECG sensor assembly serves as an aide in confirming proper placement of the catheter distal tip 76A.

In the embodiment illustrated in FIGS. 11-12E, the ECG sensor assembly includes a distal portion of the core wire 138 disposed proximate the stylet distal end 130B. The core wire 138, being electrically conductive, enables ECG signals to be detected by the distal end thereof and transmitted proximally along the core wire. A conductive material 146, such as a conductive epoxy, fills a distal portion of the sleeve 140 adjacent the distal termination of the core wire 138 so as to be in conductive communication with the distal end of the core wire. This in turn increases the conductive surface of the distal end 130B of the stylet 130 so as to improve its ability to detect ECG signals.

Before catheter placement, the stylet 130 is loaded into a lumen of the catheter 72. Note that the stylet 130 can come preloaded in the catheter lumen from the manufacturer, or loaded into the catheter by the clinician prior to catheter insertion. The stylet 130 is disposed within the catheter lumen such that the distal end 130B of the stylet 130 is substantially co-terminal with the distal tip 76A of the catheter 72, thus placing the distal tips of both the stylet and the catheter in substantial alignment with one another. The co-terminality of the catheter 72 and stylet 130 enables the magnetic assembly to function with the TLS sensor 50 in TLS mode to track the position of the catheter distal tip 76A as it advances within the patient vasculature, as has been described. Note, however, that for the tip confirmation functionality of the system 10, the distal end 130B of the stylet 130 need not be co-terminal with the catheter distal end 76A. Rather, all that is required is that a conductive path between the vasculature and the ECG sensor assembly, in this case the core wire 138, be established such that electrical impulses of the SA node or other node of the patient's heart can be detected. This conductive path in one embodiment can include various components including saline solution, blood, etc.

In one embodiment, once the catheter 72 has been introduced into the patient vasculature via the insertion site 73 (FIG. 10) the TLS mode of the system 10 can be employed as already described to advance the catheter distal tip 76A toward its intended destination proximate the SA node. Upon approaching the region of the heart, the system 10 can be switched to ECG mode to enable ECG signals emitted by the SA node to be detected. As the stylet-loaded catheter is advanced toward the patient's heart, the electrically conductive ECG sensor assembly, including the distal end of the core wire 138 and the conductive material 146, begins to detect the electrical impulses produced by the SA node. As such, the ECG sensor assembly serves as an electrode for detecting the ECG signals. The elongate core wire 138 proximal to the core wire distal end serves as a conductive pathway to convey the electrical impulses produced by the SA node and received by the ECG sensor assembly to the tether 134.

The tether 134 conveys the ECG signals to the TLS sensor 50 temporarily placed on the patient's chest. The tether 134 is operably connected to the TLS sensor 50 via the tether connector 132 or other suitable direct or indirect connective configuration. As described, the ECG signal can then be processed and depicted on the system display 30 (FIG. 9, 10). Monitoring of the ECG signal received by the TLS sensor 50 and displayed by the display 30 enables a clinician to observe and analyze changes in the signal as the catheter distal tip 76A advances toward the SA node. When the received ECG signal matches a desired profile, the clinician can determine that the catheter distal tip 76A has reached a desired position with respect to the SA node. As mentioned, in one embodiment this desired position lies within the lower one-third (⅓rd) portion of the SVC.

The ECG sensor assembly and magnetic assembly can work in concert in assisting a clinician in placing a catheter within the vasculature. Generally, the magnetic assembly of the stylet 130 assists the clinician in generally navigating the vasculature from initial catheter insertion so as to place the distal end 76A of the catheter 72 in the general region of the patient's heart. The ECG sensor assembly can then be employed to guide the catheter distal end 76A to the desired location within the SVC by enabling the clinician to observe changes in the ECG signals produced by the heart as the stylet ECG sensor assembly approaches the SA node. Again, once a suitable ECG signal profile is observed, the clinician can determine that the distal ends of both the stylet 130 and the catheter 72 have arrived at the desired location with respect to the patient's heart. Once it has been positioned as desired, the catheter 72 may be secured in place and the stylet 130 removed from the catheter lumen. It is noted here that the stylet may include one of a variety of configurations in addition to what is explicitly described herein. In one embodiment, the stylet can attach directly to the console instead of an indirect attachment via the TLS sensor. In another embodiment, the structure of the stylet 130 that enables its TLS and ECG-related functionalities can be integrated into the catheter structure itself. For instance, the magnetic assembly and/or ECG sensor assembly can, in one embodiment, be incorporated into the wall of the catheter.

FIGS. 13A-15 describe various details relating to the passage of ECG signal data from the stylet tether 134 to the TLS sensor 50 positioned on the patient's chest, according the present embodiment. In particular, this embodiment is concerned with passage of ECG signal data from a sterile field surrounding the catheter 72 and insertion site 73, which includes the stylet 130 and tether 134, and a non-sterile field, such as the patient's chest on which the TLS sensor is positioned. Such passage should not disrupt the sterile field so that the sterility thereof is compromised. A sterile drape that is positioned over the patient 70 during the catheter insertion procedure defines the majority of the sterile field: areas above the drape are sterile, while areas below (excluding the insertion site and immediately surrounding region) are non-sterile. As will be seen, the discussion below includes at least a first communication node associated with the stylet 130, and a second communication node associated with the TLS sensor 50 that operably connect with one another to enable ECG signal data transfer therebetween.

One embodiment addressing the passage of ECG signal data from the sterile field to the non-sterile field without compromising the sterility of the former is depicted in FIGS. 13A-15, which depict a “through-drape” implementation also referred to as a “shark fin” implementation. In particular, FIG. 14A shows the TLS sensor 50 as described above for placement on the chest of the patient during a catheter insertion procedure. The TLS sensor 50 includes on a top surface thereof a connector base 152 defining a channel 152A in which are disposed three electrical base contacts 154. A fin connector 156, also shown in FIGS. 13A-13D, is sized to be slidingly received by the channel 152A of the connector base 152, as shown in FIGS. 14B and 15. Two ECG lead/electrode pairs 158 extend from the fin connector 156 for placement on the shoulder and torso or other suitable external locations on the patient body. The drape-piercing tether connector 132 is configured to slidingly mate with a portion of the fin connector 156, as will be described further below, to complete a conductive pathway from the stylet 120, through the sterile field to the TLS sensor 50.

FIGS. 13A-13D show further aspects of the fin connector 156. In particular, the fin connector 156 defines a lower barrel portion 160 that is sized to be received in the channel 152A of the connector base 152 (FIGS. 14B, 15). A hole 162 surrounded by a centering cone 164 is included on a back end of an upper barrel portion 166. The upper barrel portion 166 is sized to receive the tether connector 132 of the stylet 130 (FIGS. 14C, 15) such that a pin contact 170 extending into a channel 172 of the tether connector 132 (FIG. 15) is guided by the centering hole until it seats within the hole 162 of the fin connector 156, thus interconnecting the tether connector with the fin connector. An engagement feature, such as the engagement feature 169 shown in FIGS. 13C and 13D, can be included on either side of the fin connector 156 to engage with corresponding detents 173 (FIG. 13F) on the tether connector 132 to assist with maintaining a mating between the two components. If disengagement between the two components is desired, a sufficient reverse pull force is applied to the tether connector 132 while holding or securing the fin connector 156 to prevent its removal from the channel 152A of the connector base 152.

FIG. 13D shows that the fin connector 156 includes a plurality of electrical contacts 168. In the present embodiment, three contacts 168 are included: the two forward-most contact each electrically connecting with a terminal end of one of the ECG leads 158, and the rear contact extending into axial proximity of the hole 162 so as to electrically connect with the pin contact 170 of the tether connector 132 when the latter is mated with the fin connector 156 (FIG. 15). A bottom portion of each contact 168 of the fin connector 156 is positioned to electrically connect with a corresponding one of the base contacts 154 of the TLS sensor connector base 152. In one embodiment, the bottom portion of each contact 168 includes a retention feature, such as an indentation 168A. So configured, each contact 168 can resiliently engage a respective one of the base contacts 154 when the fin connector 156 is received by the TLS sensor connector base 152 such that a tip of each base contact is received in the respective indentation 168A. This configuration provides an additional securement (FIG. 15) to assist in preventing premature separation of the fin connector 156 from the connector base 152. Note that many different retention features between the base contacts 154 and the fin contacts 168 can be included in addition to what is shown and described herein.

FIGS. 13E and 13F depict various details of the tether connector 132 according to one embodiment, including the tether connector channel 172, the pin contact 170 disposed in the channel, and detents 173 for removably engaging the engagement features 169 of the fin connector 156 (FIGS. 13A-13D), as described above. FIG. 13E further shows a plurality of gripping features 171 as an example of structure that can be included to assist the clinician in grasping the tether connector 132.

FIG. 14B shows a first connection stage for interconnecting the above described components, wherein the fin connector 156 is removably mated with the TLS sensor connector base 152 by the sliding engagement of the lower barrel portion 160 of the fin connector with the connector base channel 152A. This engagement electrically connects the connector base contacts 154 with the corresponding fin contacts 168 (FIG. 15).

FIG. 14C shows a second connection stage, wherein the tether connector 132 is removably mated with the fin connector 156 by the sliding engagement of the tether connector channel 172 with the upper barrel portion 166 of the fin connector. This engagement electrically connects the tether connector pin contact 170 with the back contact 168 of the fin connector 156, as best seen in FIG. 15. In the present embodiment, the horizontal sliding movement of the tether connector 132 with respect to the fin connector 156 is in the same engagement direction as when the fin connector is slidably mated to the sensor connector base channel 152A (FIG. 14B). In one embodiment, one or both of the stylet 130/tether connector 132 and the fin connector 156 are disposable. Also, the tether connector in one embodiment can be mated to the fin connector after the fin connector has been mated to the TLS sensor, while in another embodiment the tether connector can be first mated to the fin connector through the surgical drape before the fin connector is mated to the TLS sensor.

In the connection scheme shown in FIG. 14C, the stylet 130 is operably connected to the TLS sensor 50 via the tether connector 132, thus enabling the ECG sensor assembly of the stylet to communicate ECG signals to the TLS sensor. In addition, the ECG lead/electrode pairs 158 are operably connected to the TLS sensor 50. In one embodiment, therefore, the tether connector 132 is referred to as a first communication node for the stylet 130, while the fin connector 156 is referred to as a second communication node for the TLS sensor 50. As will be seen, various other first and second communication nodes can be employed to enable the establishment of a conductive pathway between the ECG sensor assembly and the TLS sensor or other system component.

Note that various other connective schemes and structures can be employed to establish operable communication between the stylet and the TLS sensor. For instance, the tether connector can use a slicing contact instead of a pin contact to pierce the drape. Or, the fin connector can be integrally formed with the TLS sensor. These and other configurations are therefore embraced within the scope of embodiments of the present disclosure.

As mentioned, a drape 174 is often placed over the patient 70 and employed as a barrier to separate a sterile field of the patient, e.g., areas and components above the drape and proximate to the insertion site 73 (including the catheter 72, the stylet 130, and tether 134 (FIG. 10)) from non-sterile areas outside of the sterile field, e.g., areas and components below the drape, including the patient's chest, the sensor 50 (FIG. 10) placed on the chest, and regions immediately surrounding the patient 70, also referred to herein as a non-sterile field. As seen in FIG. 15, the sterile drape 174 used during catheter placement to establish the sterile field is interposed between the interconnection of the tether connector 132 with the fin connector 156. As just described, the tether connector 132 includes the pin contact 170 that is configured to pierce the drape 174 when the two components are mated. This piercing forms a small hole, or perforation 175, in the sterile drape 174 that is occupied by the pin contact 170, thus minimizing the size of the drape perforation by the pin contact. Moreover, the fit between the tether connector 132 and the fin connector 156 is such that the perforation in sterile drape made by piercing of the pin contact 170 is enclosed by the tether connector channel 172, thus preserving the sterility of the drape and preventing a breach in the drape that could compromise the sterile barrier established thereby. The tether connector channel 172 is shaped and configured so as to fold the sterile drape 174 down prior to piercing by the pin contact 170 such that the pin contact does not pierce the drape until it is disposed proximate the hole 162 of the fin connector 156 and such that the drape does not bunch up within the channel. It is noted here that the tether connector 132 and fin connector 156 are configured so as to facilitate alignment therebetween blindly through the opaque sterile drape 174, i.e., via palpation absent visualization by the clinician of both components.

As already mentioned, note further that the fin contacts 168 of the fin connector 156 as shown in FIG. 15 include the indentations 168A, which are configured to mate with the sensor base contacts 154 in such a way as to assist in retaining the fin connector in engagement with the sensor base channel 152A. This in turn reduces the need for additional apparatus to secure the fin connector 156 to the TLS sensor 50. In other embodiments, retention features that are separate from the electrical contacts can be employed to assist in retaining the fin connector in engagement with the sensor base channel. In one embodiment, the base contacts 154 can be configured as pogo pins such that they are vertically displaceable to assist in retaining the fin connector 156.

FIG. 16 shows a typical ECG waveform 176 of a patient, including a P-wave and a QRS complex. Generally, and with respect to the present system 10, the amplitude of the P-wave varies as a function of distance of the ECG sensor assembly from the SA node, which produces the P-wave of the waveform 176. A clinician can use this relationship in determining when the catheter tip is properly positioned proximate the heart. For instance, in one implementation the catheter tip is desirably placed within the lower one-third (⅓rd) of the superior vena cava, as has been discussed. The ECG data detected by the ECG sensor assembly of the stylet 130 is used to reproduce waveforms such as the waveform 176, for depiction on the display 30 of the system 10 during ECG mode.

Reference is now made to FIG. 17 in describing display aspects of ECG signal data on the display 30 when the system 10 is in ECG mode, the third modality described further above, according to one embodiment. The screenshot 178 of the display 30 includes elements of the TLS modality, including a representative image 120 of the TLS sensor 50, with the icon 114 corresponding to the position of the distal end of the stylet 130 during transit through the patient vasculature. The screenshot 178 further includes a window 180 in which the current ECG waveform captured by the ECG sensor assembly of the stylet 130 and processed by the system 10 is displayed. The window 180 is continually refreshed as new waveforms are detected.

Window 182 includes a successive depiction of the most recent detected ECG waveforms, and includes a refresh bar 182A, which moves laterally to refresh the waveforms as they are detected. Window 184A is used to display a baseline ECG waveform, captured before the ECG sensor assembly is brought into proximity with the SA node, for comparison purposes to assist the clinician in determining when the desired catheter tip location has been achieved. Windows 184B and 184C can be filled by user-selected detected ECG waveforms when the user pushes a predetermined button on the probe 40 or the console button interface 32. The waveforms in the windows 184B and 184C remain until overwritten by new waveforms as a result of user selection via button pushes or other input. As in previous modes, the depth scale 124, status/action indicia 126, and button icons 128 are included on the display 30. An integrity indicator 186 is also included on the display 30 to give an indication of whether the ECG lead/electrode pairs 158 are operably connected to the TLS sensor 50 and the patient 70.

As seen above, therefore, the display 30 depicts in one embodiment elements of both the TLS and ECG modalities simultaneously on a single screen, thus offering the clinician ample data to assist in placing the catheter distal tip in a desired position. Note further that in one embodiment a printout of the screenshot or selected ECG or TLS data can be saved, printed, or otherwise preserved by the system 10 to enable documentation of proper catheter placement.

Although the embodiments described herein relate to a particular configuration of a catheter, such as a PICC or CVC, such embodiments are merely exemplary. Accordingly, the principles of the present invention can be extended to catheters of many different configurations and designs.

FIGS. 18-19B depict examples of contact engagement configurations for the tether connector 132 and fin connector 156. Specifically, FIG. 18 depicts the fin contacts 168 of the fin connector 156 according to one embodiment, wherein the rear contact includes a spring clip configuration 168B for receiving the pin contact 170 (FIG. 15) of the tether connector 132 via the centering cone 164 or other aperture defined in the fin connector. FIGS. 19A and 19B depict an engagement scheme according to another embodiment, wherein the pin contact 170 of the tether connector 132 includes a barbed feature 170A that, when inserted into the centering cone 164 or other aperture of the fin connector 156, engages a shoulder 168C defined on the rear fin contact 168 of the fin connector so as to help prevent premature removal of the pin contact from the fin connector. These embodiments thus serve as non-limiting examples of a variety of contact configurations that can be included with the fin connector 156, the sensor connector base 152, and the tether connector 132. Note that unless referred to as otherwise, the contacts described herein are understood to include electrical contacts used in establishing a conductive pathway.

The embodiments to be described below in connection with FIGS. 20A-32 each depict an example connection scheme as a means for establishing a conductive or other communication pathway between a patient's sterile field and a non-sterile field, i.e., areas outside of the sterile field. Thus, the embodiments described herein serve as examples of structure, material, and/or compositions corresponding to the means for establishing a conductive or other communication pathway. In particular, various embodiments described herein disclose examples for breaching or otherwise circumventing a sterile barrier separating the sterile field from the non-sterile field so as to provide at least a portion of the conductive pathway for the passage of ECG signals from a sensing component such as the ECG sensor assembly of the stylet 130 to the sensor 50, also referred to herein as a TLS sensor or chest sensor, or other suitable data-receiving component of the system 10. Note that these embodiments are merely examples of a variety of means for establishing such a conductive or other communication pathway, and are not to be considered limiting of the scope of the present disclosure. It is therefore appreciated that the means for establishing a conductive or other communication pathway can be employed for transferring ECG signals or other information, electrical signals, optical signals, etc.

As will be seen, many of the embodiments to be described include a tether connector, also referred to herein as a first communication node, which is operably connected to the stylet 130 and included in the sterile field, the tether connector is configured to operably attach to a connector included on the sensor 50 or other suitable component of the system 10, also referred to herein as a second communications node, which is disposed outside of the sterile field. Note, however, that the first communication node and second communication node are contemplated as generally referring to various connector interfaces that provide a conductive pathway from the sterile field to the non-sterile field to enable the passage of ECG signals as described above. It is appreciated that the conductive pathway is a communication pathway and includes an electrical pathway, an optical pathway, etc. Further, the communication node connection schemes described and contemplated herein can be employed with systems involving the use of modalities exclusive of ECG signals for navigation or placement of a catheter or other medical device.

Note further that the embodiments to follow that describe configurations for breaching a drape or other non-transparent sterile barrier are configured such that location of a communication node disposed out-of-sight under the drape/barrier is facilitated by palpation of the clinician, thus easing location and connection of the first and second communication nodes. Also, many of the connector configurations described herein can be configured as one-use, disposable components so as to minimize concerns with infection.

Reference is now made to FIGS. 20A-20C, which depict a connection scheme as a means for establishing a conductive pathway between sterile and non-sterile fields, according to one embodiment. In particular, FIGS. 20A-20C depict a tether connector 232 that includes an outer housing 234 and a blade holder 236 that attaches to the outer housing. A blade contact 238 is secured by the blade holder 236 such that the blade contact extends into a channel 240 of the tether connector. The blade contact 238 serves to create a slice perforation in a drape that is interposed between the tether connector and the fin connector 256 when the tether connector 232 is slid on to engage the fin connector in the manner described in previous embodiments. As before, the outer housing 234 of the tether connector envelops and protects the perforation so as to prevent contamination and compromise of the sterile field.

FIG. 20C shows that a fin connector 256 includes a fin contact 268 that is configured to physically interconnect with the blade contact 238 when the tether connector is slid on to the fin connector 256, thus establishing a conductive pathway through the sheath so as to enable ECG signals from an ECG sensing component, i.e., the ECG sensor assembly described above for instance, to pass to the sensor 50 via the blade contact 238/fin contact 268 engagement. Note that the particular configuration of the blade and fin contacts can be varied from what is described herein. For instance, the tether connector can include two or more blades or contacts for engagement with corresponding fin contacts to enable multiple conductive pathways to be established, if desired. The engagement surfaces of the tether connector and the fin connector can also vary from what is shown and described. In one embodiment, a light source can be included with the fin connector or other connectors as described herein so as to provide illumination through the drape 174 and provide visual assistance in locating the fin connector for interconnection with the tether connector.

As seen in FIGS. 14A and 14B, in one embodiment the ECG leads 158 are permanently connected to the fin connector 156. FIG. 21A depicts another possible embodiment, wherein the ECG leads are removably attached to the fin connector 156 via a connector, such as a horseshoe connector 270, best seen in FIG. 21B. FIG. 21A further shows that the fin connector 156 is permanently attached to the sensor 50. These and other variations in the connective schemes of the various components of the system 10 are therefore contemplated as falling within the scope of the present disclosure. In another embodiment, the electrode of each lead is removably attachable from the lead, such as via a snap connection, for instance.

Reference is now made to FIGS. 22A-22C, which depict a connection scheme as a means for establishing a conductive pathway between sterile and non-sterile fields, according to one embodiment. In particular, FIGS. 22A-22C depict a tether connector 332 that includes a channel 372 for slidably engaging an upper barrel 166 of a fin connector 356 disposed on the sensor 50, in a manner similar to previous embodiments. The tether connector 332 includes a bi-positional top cap 374 to which is attached a pin contact 370 or other piercing contact.

The top cap 374 is positioned in an un-actuated first position, shown in phantom in FIG. 22B, when the tether connector 332 is first slid on to the fin connector 356. The drape, removed for clarity, is interposed between the upper barrel 166 of the fin connector 356 and the tether connector channel 372, similar to earlier embodiments. After the tether connector 332 is positioned on the fin connector 356, the top cap 374 can then be depressed by the clinician into an actuated second position shown in FIG. 22B, wherein the pin contact 370 is pressed downward through the drape and into operable engagement with a corresponding contact disposed in the fin connector 356. The tether connector 332 is thus positioned as shown in FIG. 22C. In addition to establishing a conductive path through the drape 174, this engagement of the pin contact 370 locks the tether connector 332 on to the fin connector 356 so as to prevent premature separation of the components.

Reference is now made to FIGS. 23A and 23B, which depict a connection scheme as a means for establishing a conductive pathway between sterile and non-sterile fields, according to one embodiment. In particular, FIG. 23A depicts a tether connector 432 including a pin contact 440 or other suitable contact attached to an actuation assembly 442. The actuation assembly 442 includes lever arms for selectively lowering the pin contact 440 through an opening defined by a male end 448 of a housing 446 in which the actuation assembly is disposed. The male end 448 of the housing is configured to be received by a sensor connector receptacle 450 disposed on the sensor 50 or other suitable component of the system, such as a remote module operably connected to the sensor, for instance.

To interconnect the tether connector 432 to the sensor connector receptacle 450, the male end 448 of the tether connector 432 is brought, above the drape 174, into proximity with the receptacle 450. The actuation assembly 442 is then actuated by raising the lever arms 444, as shown in FIG. 23B. The pin contact 440 is forced downward through the drape 174, thus defining a perforation therein. The male end 448 can then be fully received into the sensor receptacle 450, wherein the pin contact 440 operably connects with a suitable contact of the sensor connector receptacle. The connector scheme shown in FIGS. 23A and 23B is useful for imposing a minimal downward force on the body of the patient during connector interconnection. Further, the actuation assembly 442 provides a predetermined force in connecting the first communication node (the tether connector 432) with the second communication node (the sensor connector receptacle 450), and thus does not rely on a clinician's estimation of force to establish the node connection. In another embodiment, the housing 446 and the sensor receptacle 450 can be aligned and mated before the actuation assembly 442 is actuated to pierce the contact 440 through the drape.

Reference is now made to FIG. 24, which depicts a connection scheme as a means for establishing a conductive pathway between sterile and non-sterile fields, according to one embodiment. As in the embodiment shown in FIGS. 23A and 23B, the present interconnection scheme minimizes downward pressure on the body of the patient during interconnection of the nodes. As shown, a tether connector 532 includes a pin contact 540 or other suitable contact included with a threaded cap 542, which defines threads on an inside surface thereof. The threaded cap 542 is configured to threadingly receive a threaded base 544 disposed on the sensor 50 or other suitable component of the system, such as a remote module operably connected to the sensor, for instance. As before, the drape 174 is interposed therebetween.

To interconnect the tether connector 532 to the sensor 50, the threaded cap 542 of the tether connector is brought, above the drape 174, into proximity with the threaded base 544 and threaded on to the base. This causes the pin contact 540 to penetrate the drape 174, thus defining a perforation therein. Further threading of the cap 542 on to the base 544 causes the pin contact 540 to engage a contact receptacle 546 included in the base 544, thus operably interconnecting the two nodes. In one embodiment, the tether 134 is rotatably attached to the threaded cap 542 so as to prevent twisting of the tether during threading. The connector scheme shown in FIG. 24 is useful for imposing a minimal downward force on the body of the patient during connector interconnection as the force to join the two connectors is directed laterally with respect to the patient via the threading operation. Note further that a variety of thread configurations and locations, as well as different cap and base configurations, are contemplated by the present disclosure.

Reference is now made to FIGS. 25A and 25B, which depict a connection scheme as a means for establishing a conductive pathway between sterile and non-sterile fields, according to one embodiment. As in the previous embodiment, the present interconnection scheme minimizes downward pressure on the body of the patient during interconnection of the nodes. As depicted in FIGS. 25A and 25B, a tether connector 632 includes one or more piercing contacts, such as pin contacts 640A and 640B that are respectively included on slide arms 642A and 642B. One or more contact receptacles, such as contact receptacles 644A and 644B, are included on a portion of the sensor 50, such as a sensor fin 646, or other suitable system component. As before, the drape 174 is interposed between the tether connector 632 and the sensor fin 646 to serve as a sterile barrier.

To interconnect the tether connector 632 to the sensor fin 646, the tether connector is brought, above the drape 174, into proximity with the sensor fin such that the slide arms 642A and 642B straddle the sensor fin and such that the pin contacts 640A and 640B are aligned with corresponding contact receptacles 644A and 644B, as shown in FIG. 25A. The slide arms 642A and 642B are then slid toward one another such that the pin contacts 640A and 640B penetrate the drape 174, each defining a perforation therein. The slide arms 642A and 642B are slid inward until the pin contacts 640A and 640B seat within and operably connect with the corresponding contact receptacles 644A and 644B, as seen in FIG. 25B, thus interconnecting the two nodes. The connector scheme shown in FIGS. 25A and 25B is useful for imposing a minimal downward force on the body of the patient during connector interconnection as the force to join the two connectors is directed laterally with respect to the patient. Note that the particular configuration of the tether connector, the sensor fin, and the contacts can vary from what is explicitly described herein. For instance, in one embodiment the slide arms can be configured as bi-positional rocker arms that are connected in a see-saw configuration with respect to one another. Also, one, two, or more contacts can be included on the slide arms.

Reference is now made to FIGS. 26A and 26B, which depict a connection scheme as a means for establishing a conductive pathway between sterile and non-sterile fields, according to one embodiment. As shown, an integrated connector 730 is incorporated into the drape 174 so as to enable operable interconnection therethrough. In the illustrated embodiment, the integrated connector 730 includes a conductive base portion 734 from which extend mechanical connectors, such as snap balls 736A and 736B.

As shown in FIG. 26B, the integrated connector 730 is positioned in the drape 174 as to be connectable with both a suitable receptacle 738 of a tether connector 732 and a suitable receptacle 740 of the sensor 50 or other suitable component of the system 10. In particular, the tether connector 732 can be snap-attached to the integrated connector 730, after which the integrated connector can be attached to the sensor 50, thus providing a suitable pathway for signals from the ECG sensor assembly in the sterile field to be transmitted through the sterile barrier of the drape 174 to the sensor in the non-sterile field. It is appreciated that, in other embodiments, the integrated connector can include other configurations, such as different mechanical connectors, e.g., friction connectors, male/female connectors, etc., and as such the receptacles on the tether connector and sensor can likewise be modified to accommodate the different mechanical connectors. Also, the connective scheme described above can be reversed such that the receptacles are included on the integrated connector and the snap balls on the respective tether connector and sensor. Further, though presently depicted as a unitary component, the integrated connector in other embodiments can include two or more pieces that are attached to each other through a previously defined hole in the drape during manufacture thereof. These and other variations are therefore contemplated.

Reference is now made to FIG. 27, which depicts a connection scheme as a means for establishing a conductive pathway between sterile and non-sterile fields, according to one embodiment. In detail, FIG. 27 depicts an intermediate module, i.e., ECG module 750, disposed outside of the sterile field of the patient, which is operably connected to the sensor 50 of the system 10 via a sensor cable 752. The ECG module 750 is also operably connected to the ECG leads 158. In one embodiment, the ECG module 750 includes the circuitry and other components necessary for receipt and analysis of the ECG signal detected by the ECG sensor assembly of the stylet 130. As such, a conductive pathway is established between the stylet 130 and the ECG module 750 by traversing the sterile field of the patient. In the present embodiment, this is accomplished by a tether connector 762 of the tether 134.

As depicted in FIG. 27, the tether connector 762 operably attaches to a receptacle 764 of the ECG module 750. As shown, the tether connector 762 can include a sufficiently long handle that enables the clinician to attach the sterile tether connector to the receptacle 764 of the non-sterile ECG module 750 without touching the ECG module itself, thus preventing any compromise of the sterile field. In one embodiment, the handle of the tether connector 762 can include an extendable J-hook contact, for instance, that can operably connect to a suitable contact of the ECG module.

FIG. 27 further depicts a footswitch 1116, usable with any of the embodiments described herein, which may be placed on the ground near the feet of the clinician and employed to control selected aspects of system functionality during catheter placement procedures. For instance, in one embodiment, the footswitch 1116 can be used to freeze ECG waveform images on the system display 30, or to create a printout of the display during the procedure, or even after the procedure is complete so as to provide a record of final catheter placement. Of course, the design and functionality of the footswitch can be modified in many ways from what is explicitly shown and described herein.

FIG. 28 shows another example of a tether connector that can be employed with the ECG module 750 of FIG. 27 or other suitable component of the system 10 as part of a connection scheme as a means for establishing a conductive pathway between sterile and non-sterile fields, according to one embodiment. In particular, FIG. 28 depicts a tether connector 832, which includes a handle and a barbed contact 836 or other suitable contact at a proximal end thereof. A sterile shield 838 is interposed between the handle 834 and the contact 836. The sterile shield 838 assists in protecting the hand of the clinician while inserting the contact 836 into the receptacle 764 of the ECG module 750 in a manner similar to what is shown in FIG. 27. Thus, the sterile shield 838 serves as an additional barrier to prevent inadvertent contact by the clinician with a component outside of the sterile field, such as the ECG module 750. Note that the size, shape, and particular configuration of the sterile shield and/or tether connector can vary from what is explicitly described in the present embodiment.

FIGS. 29A and 29B show yet another example of a connection scheme that can be employed with the ECG module 750 of FIG. 27 or other suitable component of the system 10 as a means for establishing a conductive pathway between sterile and non-sterile fields, according to one embodiment. In particular, FIG. 29A shows that the ECG module 750 can be enveloped by a sterile bag 850. A connector, such as the integrated connector 730 described above in connection with FIGS. 26A and 26B, can be incorporated into the bag. As shown in FIG. 29B, an inner snap ball or other mechanical connector of the integrated connector 730 can be received by the suitably corresponding receptacle 764 of the ECG module 750. The tether connector of the system 10 can then be operably connected with the outer snap ball or other connector of the integrated connector 730, thus establishing a conductive pathway between the sterile field and the non-sterile field without compromising sterility. Note that the sterile bag 850 can include any one or more of a variety of suitable materials, including plastic. Note also that the integrated connector can include other connector configurations in addition to what is explicitly described herein. In one embodiment, the sterile bag includes no integrated connector, but rather is pierced by a pin contact of the tether connector, such as the barbed contact 836 included on the tether connector 832 of FIG. 28.

Reference is now made to FIG. 30, which depicts a connection scheme as a means for establishing a conductive pathway between sterile and non-sterile fields, according to one embodiment. Specifically, the stylet 130 includes a tether connector 862 as a first communication node, as in previous embodiments. A remote sensor connector 864 is also included as a second communications node, and is operably connected to the sensor 50 of the system 10 via a remote sensor connector cable 866. The tether connector 862 and remote sensor connector 864 operably connect to one another along a connection interface 868. The drape 174 that serves as a sterile barrier is interposed between the tether connector 862 and remote sensor connector 864 at the connection interface 868, and a suitable drape piercing configuration is included with the tether connector and the remote sensor connector to establish a conductive pathway through the drape. The present embodiment thus discloses one embodiment wherein the second communication node is located remotely with respect to the sensor 50.

Reference is now made to FIG. 31, which depicts a connection scheme as a means for establishing a conductive pathway between sterile and non-sterile fields, according to one embodiment. Specifically, the present embodiment includes the tether connector 862 and the remote sensor connector 864 that operably connect to one another along the connection interface 868, as described in connection with FIG. 30, above. The remote sensor connector 864 in the present embodiment is placed proximate the catheter insertion site 73 in a region over which a fenestration 880 defined in the drape 174 (portions of the drape omitted for clarity) is positioned to enable clinician access to the insertion site during catheter placement. The remote sensor connector 864 is adhered to the patient's skin proximate the catheter insertion site 73 with the use of an adhesive, tape, etc., before the region surrounding the insertion site is sterilized in preparation for catheter insertion. Thus, when the insertion site is sterilized, the remote sensor connector 864 is also sterilized. Later, when connection of the tether connector 862 to the remote sensor connector 864 is made, the clinician can handle the latter component without compromising the sterile field of the patient. It is appreciated that the particular configurations of the tether connector and the remote sensor connector can vary while still residing within the scope of the present embodiment.

Reference is now made to FIG. 32, which depicts a connection scheme as a means for establishing a conductive pathway between sterile and non-sterile fields, according to one embodiment. Specifically, FIG. 32 shows the probe 40 employed by the system 10 for US functionality, as described above in connection with FIGS. 3A and 3B. A sterile sheath 900 is placed over the probe 40 so as to bring the probe into the sterile field of the patient. A connection interface, such as a receptacle 910, is included on the probe 900 and is configured so as to be operable connectable with a tether connector 920. In one embodiment, for example, the tether connector 920 includes a pin contact that penetrates the sterile sheath 900 to mate with the receptacle 910 in such a way as to prevent contamination of the sterile field. In this way, the tether connector 920, as a first communication node, operably connects with the probe 40, as a second communications node. In turn, the probe 40 is operably connected to the system console 20, as seen in FIG. 31 for example, so as to enable ECG signals received by the ECG sensor assembly of the stylet 130 via the tether connector 920 to be forwarded to the console, the sensor 50, or other system component for processing, as described above. In another embodiment, the receptacle 910 or other suitable connection interface can be included on the cable connecting the probe 40 to the system console 20. The particular contact configuration of the receptacle 910 and tether connector 920 can be varied according to the understanding of one skilled in the art. For instance, an integrated connector such as that shown in FIGS. 26A and 26B can be incorporated into the sterile sheath in one embodiment. Note further that, though including plastic in the present embodiment, the sterile sheath as described herein can include other suitable materials for providing sterility.

Reference is now made to FIG. 33 in describing means for establishing a conductive pathway between sterile and non-sterile fields, according to one embodiment. As shown, the tether 134 includes a wireless module 950, included within the sterile field, which serves as a first communication node for wirelessly transmitting (via RF or other suitable frequency or frequency range) ECG data received from the ECG sensor assembly of the stylet 130 to a data-receiving component as a second communication node, such as the sensor 50 or other suitable component of the system 10. A wireless module ground electrode 952 is operably connected with the wireless module 950 for placement in the sterile field proximate the catheter insertion site 73. A system ground electrode 158A extends from the sensor 50 for placement outside of the sterile field but proximate both the catheter insertion site 73 and the location of the wireless module ground electrode 952. One possible placement location for the system ground electrode 158A is beneath the patient arm, as depicted in FIG. 33. The system reference electrode 158B is placed on the lower torso of the patient 70 or other suitable location, as in previous embodiments. Note that the wireless module and system console as discussed herein can be configured in one or more of a variety of ways and include components for wireless signal transmission and reception not specifically detailed herein, such as patch or other antennas, signal transducers, etc.

With the system configured as shown in FIG. 33, the system ground electrode 158A can be electrically driven such that it produces a voltage that is sensed by the passive wireless module ground electrode 952, given its proximate location with respect to the system ground electrode. This enables both ground electrodes to be at substantially equal electric potentials, thus enabling the wireless module 950 to utilize the wireless module ground electrode 952 and the ECG signals from the ECG sensor assembly of the stylet 130, e.g., the core wire 138 (FIGS. 12C-12E) in one embodiment, to detect and wirelessly transmit the ECG data to the sensor 50 for comparison with the data sensed by the system reference electrode 158B in order to obtain the desired P-wave waveform (e.g., FIG. 16). The data comparison in one embodiment is a differential comparison between the ECG data as obtained by the ECG sensor assembly of the stylet 130, the wireless module ground electrode 952, and the system reference electrode 158B. In one embodiment, the system ground electrode 158A, like the wireless module ground electrode 952, can be passive and not electrically driven. Note also that the analog ECG data can be digitized or otherwise processed by the wireless module 950 before transmission to the sensor 50 or other system component, such as the console 20.

FIG. 34 describes yet another wireless configuration as a means for establishing a conductive pathway between sterile and non-sterile fields, according to one embodiment. As shown, a positive electrode 954A at a location A and a negative electrode 954B at a location B are included with the sensor 50 and positioned on the torso of the patient 70, while a positive wireless module electrode 956 is included with the wireless node 950, as indicated at location C, positioned on or in the patient proximate the catheter insertion site 73. The ECG sensor assembly of the stylet 130, e.g., the core wire 138 in one embodiment, serves as a negative electrode for the wireless portion of the depicted configuration, indicated at D in FIG. 34 at its final position. Note that in one embodiment the locations A and B of the electrodes 954A and 954B, respectively, can be altered on the patient body to tune the system 10 for best ECG signal reception.

In the present embodiment, the electrodes 954A and 954B serve as a first independent source for sampling bipolar ECG signals. The ECG data from these electrodes are digitized and forwarded to the console 20 or other suitable system component via the cable interconnecting the sensor 50 and the console (path 1) outside of the sterile field. The wireless module electrode 956 and the ECG sensor assembly serve as a second independent source for sampling bipolar ECG signals. The ECG data from these electrodes are digitized and forwarded wirelessly to the console 20 via the wireless module 950 (path 2) within the sterile field. Thus, in the present embodiment the wireless module 950 serves as a first communication node, and a wireless receiver of the console 20 as a second communication node for the transfer of ECG signals between the two nodes. Note that the polarities of the afore-mentioned electrodes can be reversed in other embodiments.

The ECG signals received along both paths 1 and 2 are baseline corrected by appropriate circuitry of the console 20 to adjust for DC offset and drift. After such correction, a non-changing reference, or baseline, P-wave waveform 176A from path 1 can be produced, as seen in FIG. 35A, for example. Similarly, a P-wave waveform 176B as seen in FIG. 35B is produced from path 2, which waveform changes as the stylet 130 within the catheter 72 is advanced toward the heart of the patient. During such advancement, the waveform 176B from path 2 is subtracted from the P-wave waveform 176A from path 1, employing a digital differential amplifier, for instance. This subtraction removes all common components of the waveforms represented by each of the signals, and enables the console 20 to depict via its display 30 only the differences in the two signals, as seen for example by the waveform 176C shown in FIG. 35C. The change in P-wave of the waveform from path 2 can then be easily observed during catheter advancement. Thus the present embodiment enables an easily observable digital display of ECG data to be represented while preventing a physical breaching of a sterile barrier, such as a surgical drape, for the passage of such data.

Note that in other embodiments the wireless module electrode 956 can include other configurations, including a conductive element imbedded into an introducer sheath, in contact with the bloodstream of the patient, which is commonly disposed through the insertion site 73 during catheter placement. The introducer can include a connector on a proximal portion thereof to enable a connection with the wireless node 950 to be made, in one embodiment.

Note further that one or more of a variety of wireless protocols can be employed in transmitting wireless signals in accordance with the embodiments described herein, including one or more of the IEEE 802.11 family of specifications, etc. Also note that in one embodiment the wireless module can be included in a sterile sheath, as described in previous embodiments, to bring the module within the sterile field, together with connectors for operably connecting the wireless module electrode through the sheath or included in the sheath itself. Of course, other methods for maintaining the wireless module within the sterile field can also be employed. In one embodiment, the wireless module can include buttons that further enable control of the system 10 from within the sterile field.

FIG. 36 shows that in one embodiment the sensor 50 can be retro-fitted with a wireless module 960 to enable signals received by the sensor to be wirelessly transmitted to the console 20 or other suitable component of the system 10. For instance, ECG data received by the ground and reference electrodes 158A, 158B (FIG. 34) can be received by the sensor 50 then wirelessly transmitted to the system console via the wireless module 960. The wireless module 960 can include an antenna or other transmitting component and can operably connect to the sensor 50 via a sensor cable 962 or other suitable interface. Note that the wireless module 960 can be employed in connection with other embodiments described herein, including those depicted in FIGS. 10 and 33, for instance.

FIG. 37 shows a retention feature for preventing inadvertent separation of the fin connector 156 from the sensor connector base 152 or other receptacle with which the fin connector operably connects, according to one embodiment. As shown, the fin connector 156 includes a retention arm 970 that is resiliently attached to the fin connector body. The retention arm 970 includes a tab 972 that slides over and engages a lip 974 included with the connector base 152 of the sensor 50 when the fin connector 156 is slidably received in the sensor channel 152A (FIG. 14A). The engagement of the tab 972 with the lip 974 prevents inadvertent removal of the fin connector 156 during use. When removal of the fin connector 156 from the sensor connector base 152 is desired, the retention arm 970 is lifted so as to disengage the tab 972 from the lip 974, after which the fin connector can be slid out of engagement with the sensor channel 152A. This configuration can be employed either with or independent of other retention features, such as the indentations 168A (FIG. 13D). Note that in other embodiments a variety of modifications and configurations can be employed in assisting to maintain engagement between the fin connector and the connector. For instance, the retention arm in one embodiment can be operably attached to one or more of the fin contacts 168 (FIG. 13D) such that displacement, e.g., lifting laterally moving, pinching, etc., of the retention arm or other suitable fin connector component disengages the fin contact(s) from the base contacts (FIG. 15), thus reducing the overall retention force provided by the engagement of the fin contacts with the base contacts. Note further that these principles can be applied to the other connector schemes disclosed or contemplated in addition to the fin connector described here.

In addition to the above embodiments depicting various connection schemes as means for establishing a conductive pathway between sterile and non-sterile fields, other configurations can be employed, as appreciated by one skilled in the art, for performing the same functionality. Such other configurations can include, for example, wireless transmission of ECG signals from the stylet to the sensor or the system component, the inclusion of electrically conductive thread in the drape, the inclusion of an electrically conductive window (e.g., composed of an electrically conductive plastic or foil) in the sterile drape, etc. In yet another embodiment, a proximal end of the stylet/guidewire itself can be used to pierce the drape for receipt into a connector on the sensor. In this case, no tether is included on the proximal end of the stylet, and the stylet itself serves as the conductive pathway for transmitting ECG signals from the stylet sensor assembly to the sensor on the patient's chest. Such a configuration can allow for over-the-wire placement of the catheter using a stylet/guidewire as described here. As such, the above embodiments should not be construed as being limiting of the present invention in any way.

FIG. 38 shows a catheter 982 as one example of a catheter that can be employed with the catheter placement system 10 described in the embodiments disclosed herein. The catheter 982 includes a conductive annular band 984, positioned proximate the distal end 982B (though other locations along the catheter are also possible), which serves as an ECG sensor, or electrode, for detecting ECG signals from an emitting heart node of the patient 70 when the catheter is at least partially inserted within the patient vasculature. A conductive wire 986 extends along the length of the catheter 982 and in one embodiment is embedded in the catheter wall, such as by co-extrusion for instance, for connection with external ECG signal receiving components external to the patient. Note that this is but one example embodiment of a catheter and ECG sensor electrode configuration, in addition to those described above and appreciated by one skilled in the art. Yet other possible configurations are disclosed in U.S. Patent Publication No. 2010/0222664, entitled “Catheter Assembly Including ECG Sensor and Magnetic Assemblies,” which is incorporated herein by reference in its entirety.

FIG. 39 shows the catheter 982 for use with the system 10 including an ECG sensor assembly 990 according to one embodiment, wherein the catheter includes a plurality of ECG sensors, or electrodes 994A, 994B, and 994C. The electrode 994C is positioned proximate the catheter distal end 982B, while the remaining electrodes 994A and 994B are positioned on the catheter proximal thereto. Each electrode is operably connected to a respective conductive pathway, such as a conductive wire proximally extending from the electrode along the length of the catheter so as to enable detected ECG signals to be forwarded to the external TLS sensor 50 or other suitable system component. The electrodes 994A-994C can be configured in one or more of a variety of configurations suitable to act as sensors for detecting an ECG signal of the patient's heart. Also, though shown as close-ended, the catheter 982 can be open-ended in one embodiment.

As shown in FIGS. 40A-40C, the ECG sensor assembly 990 can be employed in determining the proximity of the catheter distal end 982B to the SA node, wherein the sensor assembly of the catheter 982 includes in the illustrated embodiment two electrodes 994A and 994B. In FIG. 40A, as the catheter distal end 982B approaches the SA node, the P-waves 996A and 996B of the ECG waveforms detected by the catheter electrodes 994A and 994B, respectively, both show an increase in P-wave amplitude. Because of its relatively more proximate position to the SA node, however, the electrode 994B shows a P-wave with a relatively larger amplitude. A superposition of the P-waves 996A and 996B as detected by the system 10, for instance, is shown at 998. Observation of this relationship on the system display, for instance, can give needed information to a clinician during placement of the catheter so as to aid in advancement of the catheter distal end 982B toward the SA node.

FIG. 40B shows that when the two electrodes 994A and 994B are equidistant with respect to the SA node, the amplitudes of the P-waves 996A and 996B are approximately equal, which fact is further shown by the superposition 998 of the P-waves. In FIG. 40C, the distal electrode 994B is relatively farther from the SA node than the electrode 994A, and as such its corresponding P-wave 996B is smaller relative to the P-wave 996A. Note that the type and number of electrodes can be varied from what is shown here.

In another embodiment, a filtering process can be employed in connection with use of the ECG electrodes 994A, 994B of the catheter 982 described here, wherein portions of the ECG waveforms detected by the electrodes other than the P-wave portion are cancelled out, leaving only the differences in the detected P-waves between the two electrodes to be depicted. This process is similar to that employed in connection with FIGS. 34-35C, as described above.

FIGS. 41A-41C depict various possible states for the ECG electrode integrity indicator 186, also shown as displayed on the screenshot 178 of the system display 30 in FIG. 17. The integrity indicator 186 is an icon that is displayed on the system display 30 and is part of a connection integrity component to verify the status of the connections of the various ECG signal paths with the external sensor 50, i.e., whether the connections are closed and ready for use during catheter placement procedures. Such lead verification is helpful to avoid having to remove the sterile drape and reinitiate the placement procedure if the various ECG electrodes were not properly connected before placement of the sterile drape and establishment of the sterile field about the patient.

In FIG. 41A, the integrity indicator 186 shows that no connections to the external sensor 50 are currently closed. In contrast, FIG. 41B shows that the connection between the sensor 50 and the ECG electrodes 158 (FIG. 14B) is closed, indicated by the shaded connection symbol 1004. FIG. 41C shows in addition that the connection between the sensor 50 and the ECG sensor of the stylet 130 (e.g., the core wire 138 in FIGS. 12C and 12D via the tether 134 and tether connector 132) is closed, as indicated by the shaded connection symbol 1006. Thus, the integrity indicator view in FIG. 41A represents the connection status shown in FIG. 14A, the indicator view in FIG. 41B represents the connection status shown in FIG. 14B, and the indicator view in FIG. 41C represents the connection status shown in FIG. 14C.

The system 10 can confirm the status of the above connections in one or more of a variety of ways using connection integrity components, including capacitive or inductive sensing circuits included with the sensor 50 and/or console 20 for instance, impedance-based methods, time or frequency reflectometry techniques, etc. One possible voltage balance-based connection integrity component system is shown at 1120 in FIG. 41D. In particular, the circuitry of the system 1120 includes a first resistor pair 1122 and an amplifier 1124, such as an instrumentation amplifier, operably connected via communication lines 1126, as are the other components of the present system, as shown in FIG. 41D. A second resistor pair 1128, amplifiers 1130 and 1132, an analog-to-digital converter (“ADC”) 1134, and processor 1136 are also included in the system and interconnected as shown in FIG. 41D. The processor 1136 is included in the external TLS sensor 50 in one embodiment, but can be incorporated into other system processors or included in other components, such as the console 20 in one embodiment. The various ECG electrodes of the system 10 are shown attached to the body of the patient 70, i.e., the internal ECG sensor (E1 in FIG. 41D) such as the stylet core wire 138 in the configuration shown in FIGS. 12A-12E, and both the external reference external ECG electrode 158 (E2) and second external electrode (E3) shown in FIGS. 14A-14C.

In preparation for use of the system 10, the integrity check system 1120 can be used to ensure that the external ECG electrodes are properly connected both to the body of the patient 70 and to the external TLS sensor 50 of the system 10 in one embodiment. Reference voltage Vref, shown at 1140, is driven, such as by a voltage regulator, to a predetermined value, such as 4 volts, for instance, while the voltage at the external electrode E3 is maintained at a relatively lower value, such as 2 volts for instance. The values of the voltages V1 and V2 from the electrodes 1 and 2, respectively, in FIG. 41D are averaged to generate a common mode voltage, Vcm, indicated at 1142. In one embodiment, the processor 1136 monitors Vcm, as sampled via the ADC 1134. When the external ECG electrodes E2 and E3 are properly connected to the patient body and TLS sensor 50, Vcm will be pulled lower in value, in one embodiment approaching about 2 volts, though other values are possible. If one or both of the external electrodes E2 and E3 are not properly connected, however, Vcm will be pulled higher toward the value of Vref, or about 4 volts in the present embodiment. As such, monitoring of Vcm by the processor 1136 can determine the connectivity of the external ECG electrodes. These data relating to the connectivity status of the external ECG electrodes can be forwarded to the display 30 by the processor 1136 for depiction by the indicator 186 on the display 30 shown in FIGS. 41A-41C.

FIG. 42 shows yet another possible connection integrity component configuration according to one embodiment, wherein a passive lead continuity check system is employed, eliminating any need for injecting current into the leads that extend from the various ECG electrodes of the system 10. As shown, a radiating element 1010 is included relatively near the ECG electrode leads, such as on the sensor 50. The radiating element 1010 is configured to emit a signal of a known frequency. The ECG lead wires, such as the wires of the external ECG electrodes 158 and the tether 134, act as antennae to passively detect the signal radiated by the radiating element 1010. When the ECG leads are properly attached to the sensor 50, the antenna effect of the ECG lead wires is minimized, such that the radiating signal present on the ECG lead wires is suppressed. Sensor and/or console circuitry is configured so as to detect the radiating signal present on the ECG leads and compare it to a threshold signal level. If the detected radiating signal is above the threshold, the system reports that the ECG leads are not properly connected. When the detected signal is below the threshold, the system reports that the leads are properly connected. The present configuration is passive and does not necessitate the passing of current down the ECG leads in order to check connection integrity for the connective path check.

In one embodiment, the connection check scheme of FIG. 42 can be configured such that different graduated levels of signal present on the leads will indicate whether sub-connections upstream from the ECG electrode are closed. In another embodiment, natural signal line noise in the natural 60 Hz, 120 Hz or 180 Hz frequencies, naturally present on the lead wires, can be used for detection, thus eliminating the need for the radiating element 1010.

It is appreciated that other icons and designs can be used to implement the functionality described in connection with FIGS. 41A-41C, and that connection status checking can be varied according to modifications made to the catheter placement system. Of course, other visual or aural indications can be used to convey electrode connection status.

FIGS. 43A-43B depicts details of a stylet configuration including a mode for checking whether the stylet 130 has been inadvertently cut, such as when the stylet is undesirably left in the catheter lumen when the catheter 72 is trimmed before being inserted into the patient 70. As shown, in one embodiment, the stylet 130 can include a core wire 1014 and a plurality of magnetic elements 1016 covered by a tubing sleeve 1018, together with a conductive epoxy 1020 included at the stylet distal end. A conductive wire loop 1024 is included in the stylet and loops at the distal end 130B of the stylet 130 so as to form a circuit when suitably connected with the system 10. The conductive wire loop 1024 thus defines a continuity circuit that checks the continuity of the distal portion of the stylet. If the stylet has been inadvertently cut, such as by improper catheter trimming as shown in FIG. 43B, the loop is opened and the continuity check fails, indicating the catheter tip has been compromised. The continuity check can be performed before the catheter 72 is inserted into the patient vasculature so as to prevent catheter guidance problems after insertion. In another embodiment, the conductive wire loop 1024 could be configured so as to be exposed to the patient bloodstream and additionally serve as an ECG electrode.

FIG. 44 shows one of many possible variations to the previous embodiment, wherein the conductive wire loop 1024 is implemented as a planar wire, which has a bias toward bending within the plane of least thickness. Such a planar wire can be used in stylets that have a pre-curved configuration, such as that shown in FIG. 44. In addition, in one embodiment such a wire enables the direction of stylet bending to be controlled along one axis, if desired. Indeed, in one embodiment, tension can be imparted to the planar wire in order to cause the distal portion of the stylet 130 to selectively deflect from a straight to a curved configuration as shown in FIG. 44, for example. It should be noted that the embodiments just described can be implemented in stylets having one of a variety of configurations in terms of structure, size, etc. In other embodiments, Note that in other embodiments, other techniques can be employed to ensure the stylet has not been cut or otherwise compromised, including stylet checks using time or frequency domain reflectometry, for instance.

FIGS. 45 and 46 depict a mechanical solution for preventing unintended proximal advancement of the stylet 130 within the catheter 72. In particular, FIG. 45 shows a bulbous mechanical interference feature 1028 included on the stylet distal end 130B so as to impede retraction of the stylet into the catheter lumen. FIG. 46 shows another example, wherein the stylet distal end 130B includes a deflected extended portion interference feature 1028. Of course, mechanical interference features of many different sizes and shapes can be employed, including arrow-shaped, spherical, etc.

FIGS. 47A and 47B depict an electrical solution to assist in preventing misalignment of the distal ends of the catheter 72 and the stylet 130. As shown, a conduction band 1032 is embedded within the catheter so as to be in electrical communication with two conductive portions 1036 of the stylet 130 between which is interposed a nonconductive stylet portion 1034. When the stylet distal end 130B is properly aligned with the distal end 72B of the catheter 72, the more distal stylet conductive portion 1036 is conductively connected to the more proximal stylet conductive portion 1036 via the catheter-embedded conduction band 1032. Should the stylet and catheter distal ends 130B, 72B be misaligned, however, no such conductive path is established, and the absence of this path can be detected by the sensor 50, console 20, or other suitable component of the system 10 so as to enable its rectification.

FIG. 48 depicts one possible implementation of a dual ECG electrode assembly 1040 for placement on the skin of the patient 70 during catheter placement procedures. As shown, the assembly 1040 includes dual electrodes 1042A, 1042 B a single pad, for simplifying the ECG lead placement. Corresponding leads 1044 are also included. In other embodiments, the ECG electrode assembly can include more than two electrodes, if desired.

FIG. 49 shows one example of an external ECG external electrode assembly for placement on the skin of the patient 70, including the previously-described fin connector 156, and external ECG electrodes 158. Graphics 1048 are positioned on a surface of each electrode 158 including illustrations to assist the clinician in placing the ECG electrodes in the proper location on the patient's body. This assists clinicians who may not be familiar with the proper placement locations for the electrodes on the patient's body 70. The illustrations and particular electrode configuration can vary according to system design.

FIGS. 50-61 depict various possible implementations for displaying ECG data on a display of a catheter placement system, such as the display 30 of the system 10 of FIG. 10 for instance, for assisting a clinician in placing a catheter into the vasculature of the patient 70. In many of the implementations to follow, standard methods of presenting and displaying ECG data are improved to aid in catheter placement and confirmation of tip location. As such, the following display and computing techniques may be useful in presenting data to a clinician.

FIG. 50 shows that audible or other suitable feedback can be employed in connection with displaying an ECG trace, such as an ECG trace 1050 shown here, which is similar to the trace history window 182 depicted on the display screenshot 178 in FIG. 17. In particular, in one embodiment a sound or other indicia can be correlated to an aspect of an ECG waveform of an ECG signal. In the present embodiment, an audible cue is associated with the amplitude of a P-wave 1052 of each waveform 176 in the ECG trace 1050. As the P-wave amplitude changes as shown in FIG. 50, the audible cue can correspondingly change. The audible cue can be modulated in frequency, volume, continuity (e.g., discrete click vs. a continuous tone), etc.

FIG. 51 shows a flow chart depicting one embodiment of a method for correlating and producing audible or other feedback with respect to an aspect of the ECG waveform 176, such as the amplitude of the P-wave 1052. This method in whole or in part can be performed and/or controlled by suitable components of the system 10, e.g., circuitry included in the external sensor 50 or console 20, or other suitable catheter or medical device placement system. In stage 1056, ECG signal data is sampled in a manner such as has been described above in connection with use of the system 10 during catheter placement procedures. In stage 1058, an ECG waveform is identified from the sampled ECG signal data. In stage 1060, a P-wave portion of the ECG waveform is identified. This can be accomplished, for instance, by comparing portions of the waveform with a standard, pre-loaded P-wave template to determine the existence and location of the P-wave 1052. The amplitude peak of the P-wave is then determined in stage 1062. In stage 1064, the P-wave amplitude peak is correlated to a corresponding audible or other suitable feedback output. This stage can be predetermined and stored by the system 10, or can be dynamically controlled automatically or by user input, in one embodiment. The output is then produced in stage 1066. Note that in other embodiments the output can be other than audible as has been described, including for instance visual, light/sound combinations, mechanical movement (vibratory), and/or other sensory cues, or combinations of the foregoing.

FIGS. 52-55 give further examples of visual output that can be correlated with aspects of ECG signal data, such as P-wave amplitude of each detected ECG waveform, using the method depicted in FIG. 51. For instance, FIG. 52 shows one display implementation wherein the P-wave 1052 of each ECG waveform 176 is identified and highlighted with a color to differentiate the P-wave from other portions of the waveform. In one embodiment, the color can change according to changes in P-wave amplitude.

In FIG. 53, the peak amplitude of the P-wave 1052 in each waveform 176 is traced as a colored or shaded shadowing 1070 on the ECG trace 1050 as a function of time. In particular, during catheter insertion the P-waves 1052 of successive ECG waveforms 176 often vary in magnitude as the ECG sensor assembly of the catheter assembly (e.g., the catheter and/or stylet) approaches the SA node or other node of the heart. It is often useful to display the magnitude of the P-waves 1052 on the system display 30 as such changes take place. A line or colored bar can be used to trace out the magnitude of past peaks. In this way, a comparison between current and former peak magnitudes can be conveniently made. This display mode can be employed whether the trace move across the display or if the traces remain stationary and are refreshed by a moving bar that sweeps across the display.

FIG. 54 shows that once the P-wave 1052 falls below a previous level, another color or shade of shadowing 1070 can be used, as seen in the left-most portion of the ECG trace 1050 of FIG. 54, to illustrate the difference between the most recent peaks and previous peaks. Optionally, a horizontal line 1074 can be used to trace out the peak of each P-wave 1052, as in FIG. 55. The line 1074 can be used either with or without the shadowing 1070. Of course, many other such tracing implementations and visual indicia can be devised in accordance with these principles.

Reference is made to FIGS. 56A-57B in describing aspects of scaling control of the ECG trace 150 as displayed in the trace history window 182 of the system display 30, for instance. In typical ECG devices, the rate of ECG waveform display is constant. However, human heart rates are not constant and ECG waveform formation and spacing vary from person to person. It may be beneficial to the observer to be able to change the number of waveforms and/or amount of time waveforms are displayed on the system display 30 or other suitable device. This allows more or fewer ECG waveforms to be displayed. In one embodiment, the clinician can adjust display settings to determine how many ECG waveforms 176 are displayed or how much time the waveforms are to be displayed. In one embodiment, the user can select from a series of pre-determined, discrete display time or waveform options, or the settings can be user-defined. In another embodiment, the control over the display settings of the ECG trace 1050 can be dynamically or statically controlled autonomously by the system 10.

As examples of the above ECG trace time window variability, FIG. 56A shows the ECG waveforms 176 displayed as part of the ECG trace 1050 at a standard rate of four waveforms in the window, while FIG. 56B shows an increased ECG trace window including eight waveforms. Similarly, FIG. 57A shows ECG waveform data being displayed at a standard trace rate of five seconds, i.e., each waveform 176 remains displayed for approximately five seconds; while FIG. 57B shows the ECG waveforms displayed at a relatively longer rate of approximately 10 seconds, i.e., double the standard trace rate, such that the peaks appear relatively closer together. As shown in FIGS. 56A-57B, the physical width of the ECG trace window stays the same, with only the amount of waveforms displayed therein being modified.

FIG. 58 shows a flow chart depicting one embodiment of a method for displaying ECG signal data in the manner described above in connection with FIGS. 56A-57B. Note that this method in whole or in part can be performed and/or controlled by suitable components of the system 10, e.g., circuitry included in the external sensor 50 or console 20, or other suitable catheter or medical device placement system. In stage 1080, ECG signal data is sampled in a manner such as has been described above in connection with use of the system 10 during catheter placement procedures. In stage 1082, an ECG waveform, such as the waveform 176 in FIGS. 56A-57B, is identified from the sampled ECG signal data. In stage 1084, parameters of a display window, such as the trace history window 182 shown in FIG. 17 for displaying the ECG trace 1050 of FIGS. 56A-57B, are defined. These parameters may be, for instance, the number of ECG waveforms to be included in the window, or the amount of time each waveform remains on screen. As stage 1088 shows, the parameters can be user-defined or autonomously defined and controlled in a static (e.g., pre-set at factory) or dynamic (e.g., automatically adjusted by the system according to feedback) manner. It is appreciated that the parameters can concern other display aspects of the ECG trace or waveforms, including for example waveform height, line width, etc. Further the parameters can be defined such that zero, one, two, or more ECG waveforms are displayed in the trace window before being refreshed, for instance.

In stage 1085, the ECG waveform is displayed according to the defined display window parameters. As shown, in one embodiment stage 1085 can include stages 1086 and 1090. In stage 1086 the ECG waveform is combined with previous waveforms if permitted by the parameters defined in stage 1084. In stage 1090, the ECG waveform is displayed together with any previous waveforms as permitted by the parameters defined in stage 1084.

FIG. 59 shows an individual trace window wherein a single ECG waveform 176 is displayed and is periodically refreshed as new waveforms are identified by the system 10 during catheter placement procedures, as has been described. Such a trace window is used, for example, for the current ECG waveform window 180 and windows 184A, 184B, and 184 C of the system display 30, as reflected by the display screenshot 178 shown in FIG. 17. As has been described, the ECG waveform 176 includes the P-wave 1052, and a QRS complex 1096. A ratio between the magnitude of the peak of the P-wave 1052 and the magnitude of the QRS complex 1096 can be displayed in the trace window as a numeric (as shown in FIG. 59) or other suitable format to assist the clinician in determining the change of the ECG waveform as the catheter 72 is advanced through the vasculature of the patient 70. The ratio is updated as each new ECG waveform is depicted in the individual trace window.

FIG. 60 shows a flow chart depicting one embodiment of a method for displaying an ECG waveform in the manner described above in connection with FIG. 59. Note that this method in whole or in part can be performed and/or controlled by suitable components of the system 10, e.g., circuitry included in the external sensor 50 or console 20, or other suitable catheter or medical device placement system. In stage 1100, ECG signal data is sampled in a manner such as has been described above in connection with use of the system 10 during catheter placement procedures. In stage 1102, an ECG waveform, such as the waveform 176 in FIG. 59, is identified from the sampled ECG signal data. In stage 1104, a P-wave portion of the ECG waveform 176 is identified. This can be accomplished, for instance, by comparing portions of the waveform with a standard, pre-loaded P-wave template to determine the existence and location of the P-wave 1052.

In stage 1106, a ratio between the magnitude of the P-wave amplitude and a magnitude of the QRS complex amplitude 1096 is determined. In one embodiment, this stage may include determining the amplitude peak of the P-wave, identifying the QRS complex 1096 from the ECG waveform 176 and determining the magnitude of the QRS complex magnitude. In stage 1108, the ECG waveform 176 is displayed, such as in the current ECG waveform window 180 or one of the windows 184A, 184B, and 184 C of the system display 30 (FIG. 17). The waveform 176 can be displayed with the P-wave/QRS complex ratio data acquired via stage 1106, if desired. As shown in FIG. 60, the process flow can be looped so as to acquire and display new ECG waveforms as they are produced and detected.

Stage 1110 includes a freeze image input option, wherein a user can select the displayed ECG waveform 176 and freeze it in the display, thus interrupting the looping of the process flow, or optionally preventing newly-acquired waveforms from being displayed. Also, during the process flow stage 1112 can be executed, wherein data relating to the identified ECG waveform is sent to a storage location or device. The stored image can then be displayed if desired, such as in one of the windows 184A, 184B, and 184 C of the system display 30 (FIG. 17).

FIG. 61 shows one example of a catheter placement record 1114 that can be printed and used for record keeping/documentation purposes to verify proper placement of the catheter 72 within the vasculature of the patient 70. The record 1114 can include, in one embodiment, a beginning ECG waveform 176A representing the ECG waveform when the catheter 72 is first introduced into the patient vasculature, and a final ECG waveform 176B representing the ECG waveform when the distal end of the catheter is positioned in its desired location proximate the patient's heart or other suitable location. An image representation 120 of the sensor 50 can be included with a stylet distal end icon 114 depicted on the sensor image to represent final placement of the stylet, and thus catheter as well. Date, time, patient ID, etc. can also be included in the record 1114. In one embodiment, a location for the clinician or responsible party to sign can also be included. The record 1114 can be user-modifiable via the system 10 in one embodiment so as to allow for customization for various hospital and clinic procedures and requirements. Printout of the record 1114 can be performed via an appropriate button included on the US probe 40, system console 20, etc. In another embodiment, the footswitch 1116 shown in FIG. 27 or other suitable interface can be used to capture and print the record 1114, if desired.

FIG. 62 shows yet another example of the catheter placement record 1114 that can be printed and used for record keeping/documentation purposes to verify proper placement of the catheter 72. The record 1114 can include, in one embodiment, three windows, with each window depicting the sensor image 120 and selected tip location and ECG waveform data. For instance, the record 1114 in FIG. 62 shows a left window including the beginning ECG waveform 176A and the corresponding ECG trace 1050 when the catheter 72 is first introduced to the vasculature, a middle window including the revised ECG trace 1050 and an intermediate ECG waveform 176C representing the ECG waveform when the catheter is positioned as indicated by the stylet distal end icon 114, and a right window including the updated ECG trace 1050 and final position ECG waveform 176B representing the ECG waveform when the catheter is finally positioned as indicated by the stylet distal end icon 114. Of course, other configurations/information can be included in the record.

The various data acquired via use of the system 10 as described herein can be stored and/or evaluated for current or later use. In particular, in one embodiment both the TLS magnetic element tracking data and ECG signal detection data acquired via use of the system 10 can be stored for use as appreciated by those skilled in the art. In one embodiment, the TLS magnetic element tracking data for the catheter 72 and the ECG signal detection data can be associated with catheter position within the vasculature as a function of time so that a record of the catheter placement can be constructed in real time or at a later time via storage of the data. Such data can be stored in real time during the catheter placement procedure to operate as a fail-safe mode should the system temporarily and unexpectedly shut down during placement. Further, the data can be useful to pinpoint stylet position relative to the peak P-wave amplitude of the ECG signal by calculating the distance between the current stylet distal tip position and the position where P-wave amplitude is maximized. The data can also be employed to provide three dimensional information regarding the path along which the catheter is advanced within the patient vasculature.

FIGS. 63-104 depict yet further embodiments relating to the assisted placement of a catheter or other indwelling medical device within a body of a patient. Reference is first made to FIG. 63, which shows the catheter placement system 10 according to one embodiment. The system 10 of the present embodiment includes many of the same components as previous embodiments, with the exception of external ECG leads/electrodes, which are absent in the present embodiment.

FIGS. 64A and 64B show a distal portion of a stylet 130 for use with the system 10 shown in FIG. 63, according to one embodiment. In contrast to stylets described further above, the stylet 130 as shown here includes a plurality of electrodes disposed on the stylet configured to sense ECG signals emitted by a signal-producing node of the heart of the patient for use in guiding a catheter in which the stylet is disposed to a desired location within the vasculature. As shown, the stylet 130 includes a plurality of distal electrodes 1200 positioned proximate the distal end 130B thereof.

As shown, the distal electrodes 1200 are each configured as positive electrodes, while a counterpart negative electrode 1202 is positioned proximate the distal electrodes. Positioned proximate the counterpart electrode 1202 is a ground electrode 1204. In one embodiment, each of the aforementioned electrodes is a monopolar electrode. Further, each of the electrodes described in the illustrated embodiment is electrically connected to the system 10 via wires or other conductive pathways defined interiorly to the stylet and via a tether and tether connector in a manner similar to previous embodiments. Other conductive pathway schemes, however, can also be employed to interconnect the electrodes here to the system 10.

In greater detail, each electrode of the distal electrodes 1200 is electrically connected with the counterpart electrode 1202 such that each distal electrode forms a bipolar electrode with the counterpart electrode. The six bipolar pairs are noted on FIG. 64A. This enables each distal electrode 1200 to sense ECG signals from its respective location on the distal portion of the stylet 130.

The electrodes 1200, 1202, and 1204 in the illustrated embodiment are configured as electrodes disposed on an outer surface of the stylet 130. However, it is appreciated that the electrodes in other embodiments can be placed in other positions and can vary in polarity, position, number, type, etc. Further, note that the electrodes can be included on a guidewire received within a lumen of the catheter, or included on the catheter body itself, as will be seen in succeeding embodiments. These and other variations for the electrodes are therefore appreciated.

FIG. 64B shows that in one embodiment the stylet 130 is disposed within a lumen of the catheter 72 such that the distal portion of the stylet 130 on which the electrodes 1200, 1202, and 1204 are disposed is positioned distally past the distal end 72B of the catheter 72. This position enables the electrodes 1200 to suitably detect ECG signals. As will be seen in later embodiments, the stylet can be positioned in other relationships with respect to the catheter. Thus, the catheter 72 and stylet 130 define a catheter assembly according to one embodiment.

FIG. 65A shows that, in one embodiment, ECG signals sensed by various of the distal electrodes 1200, when the stylet 130 is disposed in the patient's vasculature in proximity to the heart, are compared to one another in order to filter out common ECG elements, thus revealing only the relative changes between the sensed ECG signals. These relative differences in the sensed ECG signals of the various of the distal electrodes 1200 can then be employed to determine the position of the stylet electrodes, and hence the distal tip of the catheter, within the vasculature.

In particular, FIG. 65A shows ECG signals sensed by two bipolar electrode pairs selected from the distal electrodes 1200 and counterpart electrode 1202: bipolar pair A including electrode number 6 of the distal electrodes and the counterpart electrode; and bipolar pair B including electrode number 5 and the counterpart electrode. During placement of the catheter, an input ECG signal is simultaneously sensed, or detected, by each of the afore-mentioned bipolar electrode pairs of the stylet 130, when within the vasculature and in sufficient proximity to the patient's heart. The input ECG signal detected by each electrode of the bipolar pair is input into an analog differential amplifier or other suitable device to yield a resultant ECG signal from the bipolar pair. The resultant ECG signal is converted from an analog signal to a digital signal by an analog-to-digital converter (“ADC”) or other suitable component. The amplifier(s) and ADC are located in the console 20 (FIG. 1) and/or sensor 50 (FIG. 63) in one embodiment. Note that the sensing of input ECG signals, passage through a differential amplifier, and digitizing the resultant ECG signal is also referred to herein as “detecting” or “sampling” of an ECG signal.

In one embodiment the resultant digital ECG signal above is aligned and conditioned so that later comparison of the signal with other resultant signals simultaneously sensed by other bipolar pairs can be suitably compared. This can be accomplished in one embodiment by linear interpolation and the use of FIR and IIR filters. Alignment and conditioning of the resultant ECG signal can be performed by other processes as well. As a result of the detecting process described above, a digital ECG waveform 176 is produced by each bipolar electrode pair A and B, as shown in FIG. 65A.

The two digitized waveforms 176, each detected by the respective bipolar pair as described above, are differentially compared to one another by suitable comparison circuitry and/or software algorithms, represented in FIG. 65A by a differential amplifier 1210. This comparison acts as a filter and removes waveform elements that are common to the two waveforms 176, thus producing a filtered waveform 1214, shown on the right side of FIG. 65A. Note that the above conditioning and differential comparisons are performed in one embodiment in the processor 22 of the console 20 (FIG. 1), sensor 50 (FIG. 63), or other suitable component of the system 10. Note further that, though performed digitally to digital ECG signals in the present embodiment, conditioning and waveform comparison can optionally be performed in analog fashion to analog ECG signals. Further comparison of the ECG signal can occur with a subset of the ECG waveform instead of the entire ECG waveform as shown in FIG. 65A.

The filtered waveform 1214 includes only elements of the compared waveforms 176 that differ from one another. In particular, the amplitudes of both the P-wave and the QRS complexes differ between the two waveforms 176 sensed by the bipolar pairs A and B shown in FIG. 65A. Thus, the filtered waveform 1214 includes both a filtered P-wave 1214A that represents the difference in P-wave amplitude between the bipolar pairs and a filtered QRS complex 1214B that represents the difference in QRS amplitude between the bipolar pairs. Particularly, the filtered P-wave 1214A includes a positive amplitude, signifying that the P-wave component of the ECG waveform 176 sensed by the bipolar pair B (electrode 5) is greater in positive magnitude relative to the P-wave component sensed by the bipolar pair A (electrode 6). Correspondingly, the filtered QRS complex 1214B includes a negative amplitude, signifying that the QRS component of the ECG waveform 176 sensed by the bipolar pair B is greater in negative magnitude relative to the QRS component sensed by the bipolar pair A.

Each of FIGS. 65B and 65C also shows resultant ECG signals detected by two bipolar electrode pairs selected from the distal electrodes 1200 and counterpart electrode 1202: in FIG. 65B, the bipolar pair A as in FIG. 65A, and a bipolar pair C including electrode number 3 (FIG. 64A) and the counterpart electrode; in FIG. 65C, the bipolar pair A as in FIG. 65A, and a bipolar pair D including electrode number 1 (FIG. 64A) and the counterpart electrode. As explained above in connection with FIG. 65A, the ECG signals are sensed by each of the bipolar electrode pairs of the stylet 130 depicted in FIGS. 65 B and 65C, then compared, digitized, and conditioned to yield the digital waveform 176. The waveforms 176 from the two bipolar pairs are then differentially compared. As before, this comparison acts as a filter and removes waveform elements common to the two waveforms 176, thus producing a filtered waveform 1214, shown on the right side of FIGS. 65B and 65C.

Note that each of the bipolar electrode pairs B, C, and D is differentially compared with the biopolar electrode pair A, which includes electrode number 6 of the distal electrodes 1200 together with the counterpart electrode 1202 of FIG. 64A. Thus the bipolar electrode pair A serves to provide a baseline ECG waveform 176, shown in each of FIGS. 65A-65C, against which the ECG waveforms 176 sensed by the bipolar electrode pairs B, C, and D can be compared to produce the filtered waveforms 1214.

In each of the ECG waveform comparisons shown in FIGS. 65A-65C, it is noted that the system 10 is configured such that the ECG signals from which the waveforms 176 are derived are sensed substantially simultaneously from each of the bipolar electrode pairs A-D.

Each of the electrode pair comparisons depicted in FIGS. 65A-65C produces the filtered waveform 1214. A suitable peak identification algorithm is then employed by the system 10 in one embodiment to identify the filtered P-wave 1214A and QRS complex 1214B in the sensed and filtered digital ECG waveform of each of the electrode pair comparisons of FIGS. 65A-65C. In one embodiment, a simple threshold level detector can be employed; in another embodiment, other peak detection processes can be employed, including those that analyze the derivative of the ECG signal or that employ convolution filtering. In one embodiment, only the R-wave component of the QRS complex, and not the entire QRS complex, is identified and filtered by the system 10.

Once it has been identified from the filtered waveform 1214 for each electrode pair comparison shown in FIGS. 65A-65C, the amplitude of the filtered P-wave 1214A for each comparison pair can be plotted versus electrode position (a “peak plot”) and displayed on the display 30 (FIG. 63) for observation by the clinician during intravascular catheter placement. In the present embodiment, the above ECG detection (sampling), conditioning, comparison, and peak detection stages are iteratively repeated for a series of heartbeats over a span of time. This enables the filtered P-wave 1214A for each comparison pair to be determined over a plurality of heartbeats with the stylet 130 positioned at a single position within the patient's vasculature. In one embodiment, the number of sampled heartbeats is seven, though the ECG signals from any number of heartbeats can be iteratively sampled.

The peak amplitude of the filtered wave 1214A over the plurality of heartbeats can be plotted as a composite peak plot and displayed as described immediately above. An example of such a peak plot 1218 is shown in FIG. 66, wherein a plot point 1220A depicts the average peak amplitude of the filtered P-wave 1214A over a succession of heartbeats via detection by the bipolar electrode number 5 and subsequent comparison with the baseline bipolar electrode number 6 and filtering out of common elements, depicted in FIG. 65A.

Correspondingly, plot points 1220B and 1220C depict the average peak amplitudes of the filtered P-waves 1214A over a succession of heartbeats via detection by the bipolar electrode numbers 3 and 1, subsequent to comparison with the baseline bipolar electrode number 6 and filtering out of common elements, depicted in FIGS. 65B and C, respectively. Note that each composite plot point 1220A-C may include a vertical white line, which indicates the spread over time between the filtered P-wave peaks for the respective bipolar electrode pair. Note further that a connecting line can extend between each plot point 1220A-C as shown in FIG. 66 to show a trend between the mean values of each filtered P-wave peak. Optionally, the above comparison and plotting can also occur for the filtered QRS complexes 1214B or a sub-set thereof, as is discussed further below.

Observation of the peak plot 1218 of FIG. 66 will indicate that the distal tip of the stylet 130 (FIG. 64A) has passed the area of maximum P-wave amplitude response, i.e., the SA node of the heart, in the present embodiment. Indeed, the peak plot 1218 indicates that the bipolar electrode number 3, represented by the plot point 1220B, is positioned most proximate the SA node, given its greater filtered p-wave amplitude relative to the other sampled bipolar electrode numbers 5 (plot point 1220A) and 1 (plot point 1220C). Thus, correlation of the position of the distal tip 72B of the catheter 72 with respect to the bipolar electrode number 3 enables a clinician to use the data represented in FIG. 66 to position the catheter distal tip as desired with respect to the SA node. The peak plot 1218 thus enables the results of ECG signal sensing described in the present embodiment to be depicted in a simplified format for easy observation and determination of catheter tip location. Further, determination of the position of the stylet 130 and the distal tip of the catheter 72 in which the stylet is disposed during a given timeframe is achieved in the present embodiment without requiring movement of the catheter. In one embodiment, the catheter and stylet are advanced after an initial position has been determined and the above method repeated to determine a new position of the stylet distal tip. This procedure can be iterated as desired to place the catheter in a desired location within the vasculature.

FIG. 67 shows a representation of the intravascular position of the catheter 72 with respect to the heart 1224, and further shows three electrode locations 1226A, 1226B, and 1226C that correspond with the positions of the bipolar electrode numbers 5, 3, and 1, respectively, as represented by the peak plot 1218. The distal tip 72B of the catheter 72 is shown advanced distally past the SA node of the heart 1224.

In one embodiment, the composite ECG signal data detected by each bipolar electrode, conditioned, and filtered as described above, can be analyzed statistically to determine the quality of the composite data. In one embodiment, this is accomplished via measurement of standard deviation of the data in each group of composite ECG signals for each electrode. The results from this analysis can be displayed to the user, in one embodiment, such as together with the peak plot 1218 for instance.

Note that the presently described embodiment employs three bipolar electrodes to compare their respective ECG signals with a baseline ECG signal to determine the position of the stylet distal tip. It is appreciated that two or more bipolar electrodes can be employed to determine stylet position. For instance, the stylet 130 shown in FIG. 64A can employ a total of five bipolar electrodes (numbers 15) for comparison with a baseline electrode (number 6). Of course, other numbers and combinations of electrodes, including monopolar electrodes, can be included on the stylet in keeping with the principles of the present disclosure. The use of the stylet described here, in connection with the described method for determining stylet placement, is useful in cases where waveform structure is variable or erratic due to erratic patient heartbeats: as the variability of the ECG signal is shared by all electrodes, the variability is eliminated via filtration. Also, though it is accomplished entirely with electrodes positioned on the stylet in the present embodiment, the filtering method in another embodiment can be employed by monopolar electrodes disposed on the stylet that are coupled with an external ECG electrode placed on the skin of the patient.

FIGS. 68A-68D show example peak plots according to one embodiment, wherein four bipolar electrodes of the distal electrodes 1200 (each coupled with the counterpart electrode 1202) are employed to determine stylet location. FIG. 68A thus depicts a stylet position wherein none of the electrodes is sufficiently close to the SA node; FIG. 68B depicts the stylet approaching the SA node; FIG. 68C depicts the stylet arriving at the SA node; and FIG. 68D depicts the distal tip of the stylet having passed the SA node.

FIGS. 69A-C provide further details regarding filtering of ECG signals received from electrodes disposed on a stylet, as described in connection with FIGS. 64A-67. FIG. 69A shows, for instance, that when two detected and conditioned ECG waveforms by stylet bipolar electrode number 3 and 4 include similar P-waves and are differentially compared at 1210, the resultant filtered waveform 1214 will include no filtered P-wave, as the P-waves from both sampled waveforms were similar and therefore removed. In FIG. 69B, the waveform 176 from bipolar electrode number 4 includes a P-wave larger relative to that of the waveform sampled by bipolar electrode number 5, resulting in a filtered waveform with a negative filtered P-wave 1214A. In FIG. 69C, the waveform 176 from bipolar electrode number 3 includes a P-wave larger relative to that of the waveform sampled by bipolar electrode number 2, resulting in a filtered waveform with a positive filtered P-wave 1214A. These relationships can be employed by the processor 22 (FIG. 1) or other suitable processing component of the system 10 to produce a peak plot such as that shown at 1218 in FIG. 66 to assist in determining stylet distal tip position, and thus catheter position, with respect to the heart.

In light of the above, FIG. 69D depicts a method 1247 for use in positioning a catheter within a vasculature of a patient including, in stage 1248 inserting a stylet including a first electrode and a spaced-apart baseline electrode into the vasculature. As discussed, the first and baseline electrodes in one embodiment are bipolar electrodes including a respective one of the distal electrodes 1200 and the counterpart electrode 1202. Additional bipolar electrodes can be employed in the method. In one embodiment, the stylet is pre-disposed within a catheter such that a distal portion thereof extends beyond the distal end of the catheter. In another embodiment, the first and baseline electrodes can be included on another portion of a catheter assembly, such as the catheter itself.

In stage 1249, a first ECG signal and a baseline ECG signal are simultaneously detected from the first bipolar electrode and the baseline bipolar electrode, respectively. In one embodiment, this stage can include sensing an input ECG signal from each monopolar electrode of the first bipolar electrode and the baseline bipolar electrode, differentially comparing the input ECG signals via an analog differential amplifier, digitizing the analog resultant ECG signal output from the amplifier, and conditioning the resultant digital ECG signal to produce the first ECG signal and the baseline ECG signal as represented by the ECG waveforms 176 (FIG. 65A).

In stage 1250, at least one element common in both the first ECG signal and the baseline ECG signal is filtered out to produce a filtered ECG signal. This filtering is represented at 1210 in FIG. 65A to produce the filtered ECG waveform 1214, as described above. In stage, 1251, data relating to the filtered ECG signal is observed to determine a position of one of the first electrode and the baseline electrode. In one embodiment, this observation is facilitated by the peak plot 1218 of FIG. 66, for instance, in the case of multiple bipolar electrode readings from the stylet. Indeed, the detection and filtering stages of the method 1247 can be performed for multiple bipolar electrodes, as described in connection with FIGS. 65A-65C to provide the peak plot 1218.

FIGS. 70A-70D depict possible screenshots 1230 that can be depicted on the display 30 of the system 10 to assist in determining catheter distal tip location during catheter placement procedures, according to one embodiment. Such screenshots serve as one option, in addition to the peak plot 1218 of FIG. 66, for displaying the information acquired from the use of the multi-electrode stylet 130 and filtering method described in connection with FIGS. 64A-67. As shown, the screenshots 1230 include a position indicator 1232 that indicates in which one of three zones the catheter distal tip is currently disposed: the SVC of the heart; proximate the SA node at the cavo-atrial junction; and proximate the atrium. The screenshots 1230 also depict a vasculature portion 1234 proximate the heart in which the distal tip of the catheter will be placed.

Thus, FIG. 70A shows that the catheter distal tip has not yet entered the portion of the vasculature proximate the heart, and as such no activity is indicated on either the position indicator 1232 or vasculature portion 1234. In FIG. 70B, the distal tip of the catheter is shown having entered the SVC; as such, an arrow on the position indicator 1232 and a dot appears in the vasculature portion 1234 to indicate the distal catheter tip. In one embodiment, the vasculature portion 1234 changes color, e.g., from blue to light green (which colors correspond with the color of the corresponding zone of the position indicator 1232), to indicate presence of the catheter. In FIG. 70C, the distal tip of the catheter is shown having arrived proximate the SA node at the cavo-atrial junction; as such, the arrow on the position indicator 1232 moves to the middle zone and the dot in the vasculature portion 1234 representing the distal tip descends further down the image. The vasculature portion 1234 can change color from light green to dark green for instance, matching the color of the middle zone of the position indicator 1232. In FIG. 70D, the arrow and dot indicate that the catheter distal tip has proceeded past the SA node and is entering the atrium. The color of the vasculature portion 1234 can change to red, for instance, to match the color of the lower zone of the position indicator 1232. Note that, generally, the catheter distal tip positions shown in the screenshots 1230 of FIGS. 70A-70D respectively correspond with the peak plots 1218 shown in FIG. 68A-68D.

FIG. 71 depicts another possible screenshot for depiction of the display 30 according to one embodiment, including not only the position indicator 1232 and vasculature portion 1234, but also icons representing the sensor 50 of the system 10 and related icons for use with the magnetic tracking modality of the system as described in previous embodiments. Further, a plurality of icons 1236 is included for assistance in operating the system 10. It should be noted that the depictions of FIGS. 70A-71 are merely examples of graphical user interfaces used to assist the clinician in placing the catheter distal tip; indeed, other interfaces and depictions can be employed to accomplish the same functionality.

FIG. 72 shows various interconnection schemes for the distal electrodes 1200 and counterpart electrode 1202 of the multi-electrode stylet 130, according to certain embodiments, wherein the solid lines indicate the various bipolar pairs of the multi-electrode stylet 130. Of course, other multi-electrode configurations in addition to those depicted here are possible.

It should be appreciated that in addition to analysis of the filtered P-wave as described in connection with FIGS. 75A-76, it is appreciated that a similar analysis of the QRS complex present in filtered waveforms can also be employed in determining stylet distal tip location, and thus catheter distal tip location. Examples of filtered QRS complexes are found at 1214B in FIGS. 65A-C. FIG. 73 shows three waveforms 176 respectively sampled by bipolar electrodes at locations 1226 proximate the heart 1224. Each of the waveforms 176 includes a QRS complex 176B, which when filtered in a manner similar to that described in connection with FIGS. 64A-67, can provide filtered QRS complex data that can be plotted in a peak plot similar to that shown at 1218 in FIG. 66 to determine stylet distal tip position, noting the fact that QRS complex amplitude generally increases as the measuring electrode advances past the SA node, as shown in FIG. 73. Optionally, the filtered QRS complex data can be used as a secondary indicator to determine stylet distal tip position, in addition to use of filtered P-wave data from multiple electrodes of the stylet distal electrodes 1200 (FIGS. 64A, 64B).

FIGS. 74A and 74B depict the stylet 130 according to one embodiment wherein a bubble tip is incorporated therewith. Note that in one embodiment, the multi-electrode stylet 130 employed in the filtering procedure discussed above in connection with FIGS. 64A-67 is positioned within a lumen of a catheter such that the distal portion of the stylet including the distal electrodes 1200, the counterpart electrode 1202, and the ground electrode 1204 are disposed distal to the distal tip of the catheter 9 (see e.g., FIG. 64B). The inclusion of a bubble tip as shown in FIGS. 74A and 74B not only provides an atraumatic surface for the distal portion of the stylet 130 to reduce the possibility of injury to the vasculature during advancement of the stylet and catheter therethrough, but also prevents the stylet electrodes from physically contacting surfaces of the vasculature, which can provide spurious ECG readings.

In greater detail, the multi-electrode stylet 130 of FIGS. 74A and 74B includes an elongate stylet body 1244 including polyamide or other suitable material, on which the various electrodes 1220, 1202, and 1204 are positioned proximate the stylet distal end 130B. A plurality of magnetic elements 144 is included with the stylet body 1244 such that the elements are interposed between the electrodes 1200, though other positional configurations are possible. Wires or other conductive pathways to communicatively couple the electrodes to the system 10 are included within the stylet body 1244 and can extend into a tether connected to a proximal end of the stylet 130 (FIG. 64B). An outer covering 1246 is included about the stylet body 1244 to provide a conduit for fluid transfer to selectively fill a balloon tip 1252, included with the outer covering, that covers the distal portion of the stylet 130. FIG. 74A shows the balloon tip 1252 deflated, while FIG. 74B shows the balloon tip inflated to provide an atraumatic stylet distal tip.

FIGS. 75A-75F depict in simplified form various stages of use of the multi-electrode stylet 130 shown in FIGS. 74A and 74B in connection with placement of a catheter. Note that the multi-electrode stylet 130 in FIGS. 75A-75F is used as a guidewire, and as such it is appreciated that, though referred to herein as a stylet, the stylet 130 and other stylet configurations described herein can also be configured as guidewires. FIGS. 75A-75F show the stylet 130 introduced into the vasculature through an introducer or other suitable device for gaining vascular access (FIG. 75A); inflation of the balloon tip 1252 to enable atraumatic advancement of the stylet to a desired location proximate the heart (FIG. 75B); advancement of the catheter 72 over the stylet (FIG. 75C) until the distal end 72B thereof contacts the stylet balloon tip 1252, which prevents further distal catheter advancement and positions the catheter as desired within the vasculature (FIG. 75D); deflation of the stylet balloon tip 1252 (FIG. 75E); and removal of the stylet 130 from the vasculature through the catheter 72.

FIGS. 76A and 76B depict an atraumatic tip for the distal end 130B of the stylet 130, according to another embodiment, including a compliant plug 1254 of silicone or other suitable compliant material positioned at the distal end of the stylet 130, and an actuation wire 1256 extending within or along the body proximally from the plug so as to enable actuation of the plug from the proximal end of the stylet. In particular, when the actuation wire 1256 is pulled distally, the plug 1254 deforms and expands radially so as to provide an atraumatic stylet tip, as shown in FIG. 76B. Release of the wire enables the plug 1254 to return to its undeformed shape, as in FIG. 76A.

FIGS. 77A and 77B depict another example of an atraumatic tip for a distal end of the stylet 130 according to one embodiment, wherein the tip includes a plurality of foldable, interlinked wire segments 1260 that are operably connected to the actuation wire 1256 extending proximally through the stylet body. When the actuation wire 1256 is selectively pulled at its proximal end, the wire segments 1260 fold up and expand radially outward to provide an atraumatic tip. In addition, as with many of the other atraumatic tip configurations herein, this tip prevents distal over-advancement of the catheter past the distal end of the stylet 130 when the stylet is used as a guidewire, as in FIGS. 75A-F. A balloon or other covering for the wire segments is included in one embodiment.

FIGS. 78A and 78B depict another example of an atraumatic tip for a distal end of the stylet 130 according to one embodiment, wherein the tip includes two or more wire loop segments 1264. One end of each wire loop segment 1264 is attached to the distal end of the stylet 130 while the other end is operably attached to the actuating wire 1256 extending proximally through the stylet body. When the actuation wire 1256 is selectively pulled at its proximal end, the wire loop segments 1264 shorten in an axial direction and extend radially outward to provide an atraumatic tip for the stylet 130. In another embodiment, the wire loop segments can be stored inside a cavity defined in the stylet body distal end.

FIGS. 79A and 79B depict another example of an atraumatic tip for a distal end of the stylet 130 according to one embodiment, wherein a wire loop 1268 is stored within a cavity defined at the distal end of the stylet tip and is operably connected to the actuating wire 1256. The wire loop 1268 is biased such that when it is pushed distally past the distal end of the stylet 130 by the actuating wire 1256, the wire loop expands to provide an atraumatic tip for the stylet. Pulling the actuating wire 1256 proximally causes the wire loop 1268 to be compressed by the body of the stylet 130 and received again therein.

FIGS. 80A and 80B depict another example of an atraumatic tip for a distal end of the stylet 130 according to one embodiment, wherein the tip includes a wire helix assembly 1270 that is operably connected to the actuating wire 1256, as in previous embodiments. The wire helix assembly 1270 is coiled up in an unfurled configuration until the actuating wire 1256 is twisted, which causes the assembly to unfurl and radially expand, thus providing an atraumatic tip for the distal end of the stylet 130. Twisting of the actuating wire 1256 in the opposite direction causes the wire helix assembly 1270 to collapse back into its unfurled configuration. It is appreciated that the wire assembly can define other shapes in addition to a helix shape.

FIGS. 81-83 depict details of an electrode for inclusion on the outer surface of the catheter 72, wherein an electrode wire 1272 extends internally, such as via the catheter lumen, from a proximal end of the catheter to a point proximate the distal end thereof. The electrode wire 1272 is then fed through the catheter wall along a path that includes a curved portion 1276, as best seen in FIG. 82, to extend through the outer surface of the catheter and define an external electrode portion 1278, best seen in FIG. 83. The distal end of the electrode wire 1272 reenters and terminates in the catheter wall. The proximal end of the electrode wire 1272 is operably connected to the system 10 via a tether and tether connector, similar to previous embodiments.

One or more such electrode wires can be included in the catheter 72 and can be used in the same manner as the distal electrodes 1200, counterpart electrode 1202, and/or ground electrode 1204 of the stylet 130 of FIGS. 64A and 64B in sensing ECG signals during catheter placement. Once the catheter 72 has been placed in its final position and the electrode portion 1278 is no longer needed, the electrode wire 1272 is pulled proximally such that it is removed from the catheter, leaving a conduit through the catheter wall. Fluid later injected through the lumen of the catheter 72 is prevented from leaking through the conduit left behind by the electrode wire 1272 by virtue of the curved portion 1276 of the conduit through the catheter wall previously occupied by the electrode wire. Specifically, the curved portion 1276 is shaped such that, when fluid is passed through the catheter lumen, the pressure exerted by the fluid causes the conduit of the curved portion 1276 to seal, preventing fluid leakage therethrough. FIG. 84 depicts details of the catheter 72 according to one embodiment, wherein a conductive body portion 1282 is longitudinally integrated into the catheter body so as to extend between the proximal and distal ends of the catheter. As shown, the conductive portion 1282 extends through the catheter wall from the interior lumen to the outer surface thereof.

FIG. 85 shows that the stylet 130 including a plurality of monopolar electrodes 1280 can be disposed within the lumen of the catheter 72, thus enabling ECG signals to be transferred through the conductive body portion 1282 of the catheter wall to the electrode(s) 1280 nearest the signal for transmission to the system 10 via a tether operably connected to the stylet 130 or other suitable conductive pathway.

FIG. 86 shows the catheter 72 according to another embodiment, wherein the catheter includes the conductive body portion 1282 as in FIG. 84, but segmented by non-conductive portions 1284, which may include portions of the catheter wall, as in the present embodiment. As in FIG. 85, the stylet 130 including a plurality of the monopolar electrodes 1280 is received within the lumen of the catheter 72 to enable ECG signals to pass through one of the segmented portions of the conductive body portion 1282 to the nearest electrode for transmission to the system 10.

FIGS. 87A and 87B depict the catheter 72 according to yet another embodiment, wherein the catheter includes a plurality of spaced-apart annular conductive portions 1288 that extend from the internal catheter lumen to the outer surface thereof, best seen in FIG. 87B. The stylet 130 shown in FIG. 87C including a plurality of monopolar electrodes 1280 can be received within the lumen of the catheter 72, as shown in FIG. 87D such that ECG signals depicted by one or more of the annular conductive portions 1288 are passed through the respective conductive portion(s) to the nearest stylet electrode. The catheter 72 shown in FIGS. 87A-87D is distally trimmable; if such trimming of the catheter 72 is necessary, the stylet 130 can be proximally withdrawn, the distal end of the catheter trimmed, and the stylet reinserted. The electrodes 1280 of the stylet can simply align with the annular conductive portions 1288 that remain after trimming. Again, the stylet described here, as in other embodiments described herein, can be configured to function as a guidewire as well as a stylet.

FIGS. 88A and 88B depict the catheter 72 according to one embodiment, wherein the catheter includes a main lumen 1290 and a stylet lumen 1292 defined within the main lumen. The stylet lumen 1292 includes a plurality of spaced apart contact holes 1296 that extend between the stylet lumen and the outer surface of the catheter 72. A stylet including one or more electrodes proximate the distal end thereof can be inserted into the stylet lumen 1292. So positioned, an electrode positioned nearest the stylet distal end can receive ECG signals through the distal end of the stylet lumen 1292, while more proximal electrodes can receive ECG signals through the nearest contact hole 1296 defined in the stylet lumen wall. In another configuration, an electrode, such as a saline column for instance, can be included at or near the distal end 72B of the catheter 72 while another electrode is included with the stylet in the stylet lumen 1292. Note that the catheter 72 is distally trimmable such that the distal contact holes 1296 remaining after distal trimming can be utilized. FIG. 88B shows the catheter 72 including a stylet lumen 1292 defining two lumens, each with a corresponding set of contact holes 1296.

FIGS. 89A and 89B depict one example of a stylet 1300 that can be movably disposed within the stylet lumen 1292. The stylet 1300 includes a conductive portion 1302 configured as an electrode to receive ECG signals through the nearest contact hole 1296 of the stylet lumen 1292, and a blocking distal tip to isolate the conductive portion from fluids that would otherwise enter the stylet lumen from the distal end thereof. So configured, the conductive portion 1302 of the stylet 1300 can be electrically isolated from an electrode positioned at the distal end 72B of the catheter 72, for instance. Again, the catheter 72 is distally trimmable, wherein the stylet 1300 can be withdrawn to the desired contact hole 1296 remaining after trimming. Note that the electrodes included on the stylet can be monopolar and/or bipolar.

FIGS. 90A and 90B show details of the catheter 72 according to one embodiment, wherein the stylet lumen 1292 includes a plurality of movable valves 1308. Each valve 1308 is disposed distal to a respective one of the contact holes 1296 and configured to remain closed unless a stylet is received through the stylet lumen 1292 to force the valve open. This enables an electrode included on the stylet to be isolated from another electrode, such as an electrode included on the distal end 72B of the catheter 72. Thus, the embodiments of FIGS. 88A-90B serve as non-limiting examples of catheter assemblies that enable multi-electrode recording of ECG signals in a distally trimmable catheter.

FIGS. 91A and 91B depict a multi-electrode stylet 1320 according to one embodiment, including a light-transmissive optical fiber 1321 on which multiple conductive channels 1322 are defined as longitudinal stripes on the outer surface of the fiber about its circumference. Such channels 1322 can include a suitable conductive material such as silver for instance, and can be deposited on the optical fiber by any suitable process, including deposition. Insulative structures can be added to the stripes 1322 in one embodiment to define an individual electrode for each channel 1322. Use of an optical fiber as the body for the stylet 1320 enables light to be transmitted therethrough while the stylet is indwelling within the vasculature of the patient. This in turn enables the stylet to be used for laser speckle imaging and other optical-based operations, some of which are described below.

FIGS. 92A and 92B show details of a connector 1326 for use in coupling the conductive channels 1322 of the stylet 1320 (FIGS. 91A, 91B) at the proximal end thereof to a tether 1334. The connector 1326 in the present embodiment defines a cavity 1328 and is hinged so as to be clasped over a portion of the proximal end of the stylet 1320 such that each contact 1330 disposed on an interior surface of the cavity contacts and electrically connects with a corresponding one of the conductive channels 1322 included on the outer surface of the stylet. As best seen in FIG. 92B with the stylet 1320 received in the cavity 1328 of the connector 1326, the contacts 1330 are sized such that a precise alignment between the conductive channels 1322 and the contacts is not necessary. Thought the stylet 1320 includes four conductive channels 1322, other numbers of channels and corresponding connector contacts are possible. In addition, in one embodiment a keying feature can be added to the stylet, the connector, or both to ensure a proper alignment between the conductive channels and the contacts of the connector.

FIG. 93 depicts a multi-electrode stylet 1340 according to one embodiment, including a light-transmissive optical fiber 1321 on which conductive channels 1342 are defined as cylindrical layers deposited on the outer surface of the fiber, alternating with interposed insulating layers 1344. Again, the conductive channels 1342 can be deposited or otherwise placed on the optical fiber via a suitable process, thus preserving the optical fiber 1321 for light transmission.

FIG. 94 depicts an assembly for performing laser speckle imaging according to one embodiment, wherein an light transmissive, optical fiber-based stylet 1350 including the optical fiber 1321 is disposed within the catheter 72, which in turn is disposed in a vessel 1352 of the patient. A laser 1354, optical detector 1356, and beam splitter 1358 are positioned in relation to a proximal end of the stylet 1350 to enable a laser beam 1359 to be transmitted through the optical fiber and distal end thereof and into the bloodstream of the vessel in which the catheter is placed. The portion of the laser beam 1359 that is reflected back from the bloodstream gives an indication of the flow direction and velocity of the bloodstream, which bloodstream factors can indicate proximity to the patient's heart. Thus, the present assembly enables the system 10 to produce data relating to catheter distal tip position.

FIGS. 95A and 95B depict a distal tip 1350B of the optical fiber-based stylet 1350 according to one embodiment, wherein a deformable membrane 1360 is included at a distal end of the optical fiber 1321. The membrane 1360 deforms according to the amount of pressure incident thereon by the bloodstream surrounding the stylet 1350 when present in the vasculature of the patient. At the same time, a laser beam or other suitable light signal 1362 is transmitted distally through the optical fiber 1321 using the laser 1354, detector 1356, and beam splitter 1358 arrangement shown in FIG. 94, for instance. The amount of light that is reflected by the membrane 1360 via the optical fiber back to the detector is dependent upon the amount of distortion of the membrane. The amount of membrane distortion can be correlated to stylet distal tip position within the vasculature, thus enabling the system 10 to depict such data and assist the clinician during catheter placement procedures.

FIG. 96 depicts a distal portion of the stylet 130 according to one embodiment, including the balloon tip 1252 described in select previous embodiments and a wire coil 1366 disposed within the balloon tip. The wire coil 1366 is configured to flex and deform according to pressure and flow direction changes present within the vasculature during heartbeats. The wire coil 1366 in one embodiment is placed in AC resonance via interconnection with the system 10 such that increases or decreases in inductance of the coil can be measured by the system and interpreted to provide useful information to the clinician regarding distal tip location during catheter placement procedures.

FIG. 97 depicts a hybrid stylet 1370 according to one embodiment, extending from a lumen at the distal end of the catheter 72. The stylet includes an elongate first stylet body 1374 and an elongate second stylet body 1376 positioned side-by-side with the first stylet body. An outer covering 1378 envelops both stylet bodies 1374, 1376 and further defines a balloon tip 1380 for selective inflation to provide an atraumatic stylet distal tip. The stylet 1370 further includes a position locking balloon 1382 that is disposed proximal to the exposed portion of the stylet shown in FIG. 97 such that it remains within the lumen of the catheter 72. Like the balloon tip 1380, the position locking balloon 1382 is selectively inflatable, and engages the inner surfaces of the catheter lumen to prevent longitudinal movement of the stylet 1370 with respect to the catheter while inflated. One or more fluid vents 1384 are employed to fill the balloon tip 1380 or the position locking balloon 1382 with saline or other suitable fluid.

The first stylet body 1374 in the illustrated embodiment includes a plurality of magnetic elements 144, described further above, while the second stylet body 1376 includes the distal electrodes 1200, the counterpart electrode 1202, and the ground electrode 1204.

In addition, the second stylet body 1376 includes a magnetic flow assembly 1390 for magnetically sensing the flow of blood past the assembly in order to assist in determining stylet distal tip position within the vasculature. The magnetic flow assembly 1390 disposed on the second stylet body 1376 includes two magnetic flow coils 1392 interposed with two magnetic flow electrodes 1394. So configured, the hybrid stylet 1370 includes multiple modalities for assisting with catheter distal tip placement via stylet distal tip location, including magnet tracking via the magnetic elements 144, ECG-assisted tracking via the electrodes 1200, 1202, and 1204, and magnetic blood flow sensing via the magnetic flow assembly 1390. It is appreciated that other modalities can be included with the stylet, including laser speckle imaging as described in connection with FIG. 94, for instance.

FIG. 98 shows the hybrid stylet 1370 received within the catheter 72. FIG. 98 further shows that the proximal end of the hybrid stylet 1370 is operably connected to the tether 134, which in turn is operably connected to the tether connector 132, configured here according to one embodiment. As shown, the tether connector 132, which in the present embodiment is configured to slidably and operably connect with a corresponding connector on the sensor 50 (FIG. 63) for instance, defines a channel 1420 in which a male contact member 1422 is disposed and configured for operably mating with a corresponding female member included with the sensor connector. The contact member 1422 includes a plurality of contacts 1424, including contacts 1424A that are operably connected to the electrodes 1200, 1202, and 1204 of the second stylet body 1376, and contacts 1424B that are operably connected to the components of the magnetic flow assembly 1390. It is appreciated that the connector and contact configuration disposed therewith can take one of many possible forms. FIG. 98 further shows a pivot wire 1430 extending from one of the catheter extension legs 74B to assist in navigating the catheter distal tip during advancement through the vasculature.

FIGS. 99A and 99B depict a catheter 1450 according to one embodiment, wherein a plurality of electrodes 1456 is disposed in the catheter wall proximate the distal end thereof. A corresponding plurality of contacts 1458 are included on a bifurcation hub 1454A of the catheter 1450, each contact being operably connected to a corresponding one of the electrodes 1456 such that ECG signals sensed by the electrodes can be communicated to the respective contacts 1458. In FIG. 99B, a wireless monitoring dongle 1460 is shown attached to the bifurcation hub 1454A so as to electrically connect with the contacts 1458 thereof. The dongle 1460 can monitor data received at the contacts 1458 from the electrodes 1456, such as ECG signals, etc., and can wirelessly transmit the data to the console 20 or other component of the system 10 for processing. In one embodiment, the wireless dongle 1460 can be employed to monitor ECG signals sensed by the distal electrodes 1456 for the catheter 72 after a period of indwelling within the patient's body to confirm that the distal tip of the catheter is still positioned as desired with respect to the heart.

FIGS. 100A-100C depict one embodiment for sensing fluid flow through a catheter, such as the catheter 1450 shown in FIGS. 99A and 99B, for instance. Two leaf valves 1464 are disposed in a lumen of the catheter and each includes a magnetic element 1466 at the distal end thereof. One or more magnetic sensors 1468 are positioned on an outer wall of the catheter or in a suitable relation to the magnetic elements 1466 of the leaf valves. The leaf valves 1464 are biased closed when no fluid is flowing through the catheter lumen. When fluid flow does occur, the leaf valves are forced open, bringing the magnetic elements 1466 thereof into proximity with the magnetic sensors 1468. A signal may then be produced and/or sent by the magnetic sensors 1468 to be received by a component, such as the wireless monitoring dongle 1460 of FIG. 99B for instance, to record when and for how long the catheter lumen was in use. Such statistics or other data produced by the magnetic sensors 1468 can be compiled by the wireless monitoring dongle 1460 and/or by the system 10 if desired.

FIG. 101 depicts another embodiment for sensing fluid flow through a catheter, such as the catheter 1450 shown in FIGS. 99A and 99B, for instance. A light source 1472 is positioned on one side of the catheter wall to send a light beam 1472A to an optical sensor 1474 disposed on an opposite side of the catheter wall. Attenuation of the light signal received by the optical sensor 1474 can indicate fluid flow through the catheter. These data can be forwarded to a monitoring device, such as the wireless monitoring dongle 1460 shown in FIG. 99B, for instance. Such data can also be forwarded and compiled and/or stored by the system 10.

FIGS. 102A-102C depict details of a wireless dongle 1480 configured for use with the system 10. The dongle 1480 in one embodiment is configured to sit atop a stand 1482 included on the console 20 or other location. As shown in FIGS. 102B and 102C, the dongle 1480 is configured to operably attach to a tether connector 1484 so as to operably connect via the tether 134 with a stylet, such as those depicted in previous embodiments. So configured, the dongle 1480 can be employed to transmit ECG signal data sensed by the one or more stylet electrodes to the system 10 for processing, as had been described. The dongle 1480 further includes control buttons 1486 to enable the dongle to control functionality of the system 10 from the sterile field of the patient.

FIGS. 103A-103E show one method for placing the wireless dongle 1480 in a sterile bag 1490 in preparation for use during a catheter placement procedure: a user holding the sterile bag grasps the dongle 1480 as is sits on the stand 1482 (FIGS. 103 A, 103B). The user lifts the sterile bag 1490 and dongle 1480 from the stand 1482 (FIG. 103C), then seals the bag with the other hand (FIG. 103D). The tether connector 1484 is then operably connected to the dongle 1480 by piercing the sterile bag 1490 in such a way as to cover the breach and prevent compromising of the sterile barrier defined by the bag. The dongle 1480 is then ready for use.

FIG. 104 shows use of the dongle 1480 according to another embodiment, wherein the dongle can include an optical measurement device for calculating the approximate length of the catheter to be inserted into the patient by optically measuring on the skin from the intended insertion site to the region of final catheter distal tip placement. Such measurement by the dongle would occur prior to placing the dongle 1480 in the sterile bag 1490 (FIGS. 103A-E). In one embodiment, the dongle 1480 emits a laser dot or other light form on to the skin, which is then tracked by the dongle as it is moved along the body to the intended final location. The length, once determined by the dongle 1480, can be wirelessly transmitted to the system 10, where the calculated length of the catheter is depicted on the display 30.

Embodiments of the present invention may comprise a special purpose or general-purpose computer including computer hardware. Embodiments within the scope of the present disclosure also include computer-readable media for carrying or having computer-executable instructions or data structures stored thereon. Such computer-readable media can be any available media that can be accessed by a general purpose or special purpose computer. By way of example, and not limitation, computer-readable media can include physical (or recordable-type) computer-readable storage media, such as, RAM, ROM, EEPROM, CD-ROM or other optical disk storage, magnetic disk storage or other magnetic storage devices, non-volatile and flash memory, or any other medium which can be used to store desired program code means in the form of computer-executable instructions or data structures and which can be accessed by a general purpose or special purpose computer.

In this description and in the following claims, a “network” is defined as one or more data links that enable the transport of electronic data between computer systems and/or modules. When information is transferred or provided over a network or another communications connection (either hardwired, wireless, or a combination of hardwired or wireless) to a computer, the computer properly views the connection as a computer-readable medium. Thus, by way of example, and not limitation, computer-readable media can also include a network or data links which can be used to carry or store desired program code means in the form of computer-executable instructions or data structures and which can be accessed by a general purpose or special purpose computer.

Computer-executable instructions comprise, for example, instructions and data which cause a general purpose computer, special purpose computer, or special purpose processing device to perform a certain function or group of functions. The computer executable instructions may be, for example, binaries, intermediate format instructions such as assembly language, or even source code. Although the subject matter has been described in language specific to structural features and/or methodological acts, it is to be understood that the subject matter defined in the appended claims is not necessarily limited to the described features or acts described above. Rather, the described features and acts are disclosed as example forms of implementing the claims.

Those skilled in the art will appreciate that the embodiments of the present invention may be practiced in computing environments with one or more types of computer system configurations, including, personal computers, desktop computers, laptop computers, message processors, hand-held devices, multi-processor systems, microprocessor-based or programmable consumer electronics, network PCs, minicomputers, mainframe computers, mobile telephones, PDAs, pagers, and the like. Embodiments may also be practiced in distributed system environments where local and remote computer systems, which are linked (either by hardwired data links, wireless data links, or by a combination of hardwired and wireless data links) through a network, both perform tasks. In a distributed system environment, program modules may be located in both local and remote memory storage devices.

Embodiments of the invention may be embodied in other specific forms without departing from the spirit of the present disclosure. The described embodiments are to be considered in all respects only as illustrative, not restrictive. The scope of the embodiments is, therefore, indicated by the appended claims rather than by the foregoing description. All changes that come within the meaning and range of equivalency of the claims are to be embraced within their scope. 

What is claimed is:
 1. A catheter placement system configured for positioning a catheter within a vasculature of a patient, comprising: a console having a display; a plurality of electrodes located at a distal end of the catheter, of each the plurality of electrodes configured for sensing separate ECG signals of the patient, and the plurality of electrodes being operably connected to the console; and a processor included with the console, the processor: (i) performing a differential comparison of a plurality of ECG signals sensed by a subset of the plurality of electrodes with a baseline ECG signal sensed by a baseline electrode of the plurality of electrodes to determine resultant ECG signals and a position of the distal end of the catheter based on at least one of the resultant ECG signals; (ii) identifying an amplitude of a P-wave from each of the resultant ECG signals; and (iii) generating an output for the display that plots the amplitudes of the P-wave from the resultant ECG signals according to a position of each of the plurality of electrodes on the catheter.
 2. The catheter placement system as defined in claim 1, wherein the processor implements an algorithm for performing the differential comparison that provides the resultant ECG signals, the resultant ECG signals providing information relating to the position of the distal end of the catheter with respect to a node of the patient's heart producing the plurality of ECG signals.
 3. The catheter placement system as defined in claim 2, wherein the resultant ECG signals include only differences between the plurality of ECG signals and the baseline ECG signal.
 4. The catheter placement system as defined in claim 3, wherein the resultant ECG signals differences in amplitude of at least one of a P-wave and a QRS complex between each of the plurality of ECG signals and the baseline ECG signal.
 5. The catheter placement system as defined in claim 1, wherein the plurality of electrodes is disposed on a stylet removably positionable within a lumen of the catheter and further includes a plurality of distal electrodes of a first polarity disposed proximate a distal end of the stylet, a counterpart electrode of a second polarity, and a ground electrode.
 6. The catheter placement system as defined in claim 5, wherein the plurality of distal electrodes and the counterpart electrode cooperate to define a plurality of bipolar electrodes.
 7. The catheter placement system as defined in claim 6, wherein six bipolar electrodes are included on the stylet, including six distal electrodes of a positive polarity and a proximally disposed counterpart electrode of a negative polarity.
 8. The catheter placement system as defined in claim 5, wherein the stylet further includes at least one magnetic element for enabling tracking of the stylet by an external sensor.
 9. The catheter placement system as defined in claim 1, wherein the plurality of electrodes include monopolar electrodes that are disposed on a stylet removably positionable within a lumen of the catheter, and wherein the catheter includes at least one conductive feature to enable transfer of ECG signals through the catheter to at least one of the electrodes.
 10. The catheter placement system as defined in claim 1, wherein the plurality of electrodes are operably connected to the console via a wirelessly transmitting dongle.
 11. The catheter placement system as defined in claim 1, wherein the plurality of electrodes are positioned in a known relation to the distal end of the catheter in which each electrode is differently spaced from the distal end of the catheter.
 12. The catheter placement system as defined in claim 1, wherein the plurality of electrodes are configured for insertion into the vasculature of the patient, and the differential comparison between each of subset of the plurality of ECG signals and the baseline ECG signal comprises differences in amplitude. 